Processes for making cyclic lipid implants for intraocular use

ABSTRACT

Biocompatible implants comprising a cyclic lipid therapeutic agent are made using a low temperature melt extrusion process. The implants are suitable for intraocular use to treat an ocular condition.

CROSS REFERENCE

This application is a continuation of U.S. patent application Ser. No.16/600,732, filed Oct. 14, 2019, which is a continuation of U.S. patentapplication Ser. No. 14/876,436, filed Oct. 6, 2015, now U.S. Pat. No.10,441,543, issued Oct. 15, 2019, which is a continuation of U.S. patentapplication Ser. No. 14/469,764, filed Aug. 27, 2014, now U.S. Pat. No.9,149,428, issued Oct. 6, 2015, which is a divisional of U.S. patentapplication Ser. No. 11/612,928, filed Dec. 19, 2006, now U.S. Pat. No.8,846,073, issued Sep. 30, 2014, the entire contents of which are herebyincorporated by reference.

BACKGROUND

The present invention relates to processes for making an intraocularimplant and the implants thereby made. In particular, the presentinvention relates to low temperature processes for making implantssuitable for intraocular use.

It is known to make drug delivery systems suitable for intraocular use(“implants”). An implant can comprise one or more therapeutic agents aswell as one or more biodegradable or non-biodegradable carriers (such asa polymeric or non-polymeric carrier). Typically, the carrier comprisesthe bulk (i.e. more than 50%) of the implant by weight and can functionto hold (the carrier function) and then release the therapeutic agent invivo, for example as a biodegradable or bioerodible carrier is degradedin situ at or in proximity to the ocular tissue target site.Biocompatible implants for placement in the eye have been disclosed in anumber of patents, such as U.S. Pat. Nos. 4,521,210; 4,853,224;4,997,652; 5,164,188; 5,443,505; 5,501,856; 5,766,242; 5,824,072;5,869,079; 6,074,661; 6,331,313; 6,369,116; and 6,699,493.

Implants suitable for intraocular use have been made by various methodsincluding compression, solvent evaporation and extrusion methods. Anextrusion method for making an intraocular implant can be carried out byfirst mixing a therapeutic agent with a polymer or polymers. Typically,solid forms (i.e. powders) of the therapeutic agent and the polymers aremixed together to achieve a homogenous mixture of the powders. As noted,the polymer can function as a carrier for the therapeutic agent. Thus,if a biodegradable polymer is used the therapeutic agent can diffuse outof the polymer upon intraocular insertion or implantation of theimplant, as the polymer degrades. Although the therapeutic agent-polymermixture can be compressed to form a tablet, an extruded implant canexhibit a more desirable release profile for the therapeutic agent.Hence, an implant with superior characteristics can be made by heatingthe therapeutic agent-polymer mixture to the temperature at which thepolymer melts, followed by extrusion of an implant with desireddimensions. Melting the polymer helps ensure an even distribution of theactive agent within the polymeric matrix and upon cooling provides asolid form implant. It is known to make extruded implants forintraocular use in which the therapeutic agent-polymer mixture is heatedto about 90° C. to about 115° C. prior to being extruded. See egpublished U.S. patent application number 20050 048099.

Unfortunately heating the therapeutic agent-polymer mixture to atemperature at which the polymer melts can have undesirable ordestabilization effects. For example, heating the polymer to its melttemperature can result in the formation of degradation products and/oraggregates of either or both the therapeutic agent and the polymer. Thiscan result in the materials potentially toxic or immunogenic tosensitive ocular tissues and/or can interfere with obtaining a desiredrelease profile of the therapeutic agent from the extruded implant.Additionally, heating the therapeutic agent to the melt temperature ofthe polymeric carrier (so as to provide a homogenous dispersion of thetherapeutic agent in the polymeric matrix) can reduce the potency of aheat sensitive therapeutic agent, thereby reducing the therapeuticefficacy of the resulting implant.

Another problem with existing implants can arise from the presence ofpolymorphs of the therapeutic agent. A polymorph is a substance whichhas a chemical composition identical to that of another substance butwhich exists in a different crystal structure (eg diamond and graphite).Different polymorphs of a substance can have different stabilities,solubilities and, for a therapeutic agent, different potencies ortherapeutic efficacies. With known implants, a crystalline therapeuticagent is typically melted along with its polymeric matrix and mayrecrystallize upon formation of the solid implant. Alternately, thecrystalline therapeutic agent can be mixed with the polymer withoutmelting the therapeutic agent. In either case, the therapeutic agent ispresent in the final implant as crystals (i.e. as particles) of thetherapeutic agent dispersed throughout the polymeric matrix. Hence, witheither known method for making an implant the therapeutic agent ispresent in polymorphic forms, each of which therapeutic agent polymorphcan have a different therapeutic efficacy.

Hypotensive therapeutic agents are useful in the treatment of a numberof various ocular hypertensive conditions, such as post-surgical andpost-laser trabeculectomy ocular hypertensive episodes, glaucoma, and aspresurgical adjuncts. Glaucoma is a disease of the eye characterized byincreased intraocular pressure. On the basis of its etiology, glaucomahas been classified as primary or secondary. For example, primaryglaucoma in adults (congenital glaucoma) may be either open-angle oracute or chronic angle-closure. Secondary glaucoma results frompre-existing ocular diseases such as uveitis, intraocular tumor or anenlarged cataract.

The increased intraocular pressure characteristic of glaucoma can be dueto the obstruction of aqueous humor outflow. In chronic open-angleglaucoma, the anterior chamber and its anatomic structures appearnormal, but drainage of the aqueous humor is impeded. In acute orchronic angle-closure glaucoma, the anterior chamber is shallow, thefiltration angle is narrowed, and the iris may obstruct the trabecularmeshwork at the entrance of the canal of Schlemm. Dilation of the pupilmay push the root of the iris forward against the angle, and may producepupillary block and thus precipitate an acute attack. Eyes with narrowanterior chamber angles are predisposed to acute angle-closure glaucomaattacks of various degrees of severity.

Secondary glaucoma is caused by any interference with the flow ofaqueous humor from the posterior chamber into the anterior chamber andsubsequently, into the canal of Schlemm. Inflammatory disease of theanterior segment may prevent aqueous escape by causing completeposterior synechia in iris bombe and may plug the drainage channel withexudates. Other common causes are intraocular tumors, enlargedcataracts, central retinal vein occlusion, trauma to the eye, operativeprocedures and intraocular hemorrhage.

Considering all types together, glaucoma occurs in about 2% of allpersons over the age of 40 and may be asymptotic for years beforeprogressing to rapid loss of vision. In cases where surgery is notindicated, topical beta-adrenoreceptor antagonists have traditionallybeen the drugs of choice for treating glaucoma.

Some prostaglandins are utility as ocular hypotensive agents, includingPGF_(2α), PGF_(1α), PGE₂, and certain lipid-soluble esters, such as C₁to C₅ alkyl esters, e.g. 1-isopropyl ester, of such compounds.Unfortunately, ocular surface (conjunctival) hyperemia and foreign-bodysensation have been consistently associated with topical ocular use ofprostaglandins as anti-hypertensive agent (i.e. to treat glaucoma),including PGF_(2α) and its prodrugs, e.g. its 1-isopropyl ester. ThePGF_(2α) derivative latanoprost is sold under the trademark Xalatan® fortreating ocular hypertension and glaucoma. Topical use of latanoprostcan have the undesirable side effect of turning the iris of a userbrown.

In Laedwif M. S. et al., PROSTAGLANDINS LEUKOT. ESSENT. FATTY ACIDS72:251-6 (April 2005), it was disclosed that infusion of with a cycliclipid (prostaglandin E1) in patients with age-related maculardegeneration (ARMD) resulted in an improvement in visual acuity.

Bimatoprost is an analog (that is a structural derivative) of anaturally occurring prostamide. The formula for bimatoprost (C₂₅H₃₇NO₄)is((Z)-7-[1R,2R,3R,5S)-3,5-Dihydoxy-2-[1E,3S)-3-hydroxy-5-phenyl-1-pentenyl]cyclopentyl]-5-N-ethylheptenamide.Its' molecular weight is 415.58. Bimatoprost is a heat sensitivemolecule, meaning that it can degrade if heated to a temperature greaterthan about 65° C. In a low pH environment bimatoprost can degrade at alower temperature and at a faster rate. Bimatoprost has severalpolymorphic crystal structures. Not all the polymorphs of bimatoprosthave the same level of biological activity. Bimatoprost is slightlysoluble in water (by definition 3 mg of a water soluble substance can bedissolved in one mL of water at 25° C.).

Bimatoprost can be used to reduce intraocular pressure. See eg Cantor,L., Bimatoprost: a member of a new class of agents, the prostamides forglaucoma management, Exp Opin Invest Drugs (2001); 10(4): 721-731, and;Woodward D., et al., The Pharmacology of Bimatoprost (Lumigan™), SuryOphthalmol 2001 May; 45 (Suppl 4): S337-S345. An ophthalmic solution of0.03% bimatoprost is sold by Allergan (Irvine, Calif.) under thetrademark Lumigan®. Lumigan® is an effective treatment for ocularhypotension and glaucoma and is administered topically to the effectedeye topically once a day. Each mL of Lumigan® contains 0.3 mg ofbimatoprost as the active agent, 0.05 mg of benzalkonium chloride (BAK)as a preservative, and sodium chloride, sodium phosphate, dibasic;citric acid; and purified water as inactive agents.

It is known to make bimatoprost containing implants for intraocular use.See eg U.S. patent application Ser. Nos. 10/837,260 and 11/368,845.

Polymer Solubility Parameters

A solubility parameter for a substance is a numerical value whichindicates the relative solvency behavior of that substance. Thesolubility parameter is derived from the cohesive energy density of thesubstance, which in turn is derived from the heat of vaporization. Theheat of vaporization of a substance is the energy required to vaporize(render into a gas) the substance. From the heat of vaporization (incalories per cubic centimeter of a liquid substance), one can derive thecohesive energy density (c):

$\begin{matrix}{c = \frac{{\Delta\; H} - {RT}}{V_{m}}} & (1)\end{matrix}$

where: c=cohesive energy density; ΔHv=heat of vaporization; R=a gasconstant; T=Temperature, and Vm=molar volume. The cohesive energydensity (c) of a liquid is a numerical value that indicates the energyof vaporization in calories per cubic centimeter, and is a directreflection of the degree of van der Waals forces holding the moleculesof the liquid together. Since the solubility of two materials is onlypossible when their intermolecular attractive forces are similar,materials with similar cohesive energy density values are miscible ineach other.

The square root of the cohesive energy density (c) provides a solubilityparameter for a substance:

$\begin{matrix}{ = {\sqrt{c} = \left\lbrack \frac{{\Delta\; H} - {RT}}{V_{m}} \right\rbrack^{1/2}}} & (2)\end{matrix}$

This solubility parameter can be represented as delta (δ). δ can beexpressed in calories/cc (the standard or older parameter) or instandard international units (SI units). The SI unit is in pascals.Thus, one MPa is one milliPascal. SI parameters are about twice thevalue of the standard solubility parameter units:

δ/cal^(1/2) cm^(−3/2)=0.48888×δ/MPa^(1/2)  (3)

δMPa^(1/2)=2.0455×δ/cal^(1/2) cm−^(3/2)  (4)

The newer SI units for the solubility parameter of a substance areusually designated as δ/MPa^(1/2) (sometimes shown in a shorthandversion as just MPa^(1/2)) or δ(SI).

Since a polymer will typically decompose before its heat of vaporizationcould be measured, swelling behavior is one of the ways that asolubility parameter can be determined for a polymer. The term cohesionparameter can be used to mean the solubility parameter of a non-liquidmaterial. The solubility parameters for biodegradable polymers can bedetermined. See e.g. Siemann U., Densitometric determination of thesolubility parameters of biodegradable polyesters, Proceed Intern SympControl Rel Bioact Mater 12 (1985):53-54. As noted above, MPa^(1/2) is astandard unit for solubility parameter. The solubility parameter δ isequal to c^(1/2), where c=(ΔE/Vm)^(1/2). In short two materials will mixif their ΔG<0, and ΔG=ΔH-T ΔS (this is the formula for Gibbs Free Energy[ΔG] which defines the free energy of a reaction, where ΔH is the changein enthalpy in a constant pressure process and ΔS is the change inentropy). ΔS is always positive for mixing, but ΔH depends roughly onΔH˜Vmφ₁φ₂(δ₁-δ₂)^(1/2) where “1” and “2” are the two components. Thecloser the δ's are to each other, the closer ΔH is to zero and the moreenergetically favorable the combination.

A solid solution is a solid state solution of one or more solutes in asolvent. A solute initially in a crystalline form which enters intosolid solution is no longer in a crystalline form, as is it in asolution, albeit in this case in a solid state solution. Some mixtureswill readily form solid solutions over a range of concentrations, whileother mixtures will not form solid solutions at all. The propensity forany two substances to form a solid solution is a complicated matterinvolving the chemical, crystallographic, and quantum properties of thesubstances in question. For example, solid solutions can form if thesolute and solvent have similar atomic radii (15% or less difference),same crystal structure, similar electronegativities and/or similarvalance. It is known to compare the solubility parameters of a watersoluble drug and a single polymeric excipient to determine if they aremiscible in each other so that a glass solution will be formed upon meltextrusion. Forster, A., et al., Selection of excipients for meltextrusion with two poorly water-soluble drugs by solubility parametercalculation and thermal analysis, Int J Pharmaceutics 226 (2001)147-161. The ability of one solid to function as a cosolvent (i.e. tosolubilize) of another solid (i.e. a polymer) upon formation of a solidsolution of the two solids can depend upon the ability of the cosolventto function as a plasticizer of the polymer and/or due to the relativesimilarities of their solubility parameters.

Polyethylene glycol

Polyethylene glycol (“PEG”) has the general formulaC_(2n)H_(4n+2)O_(n+1), which can be represented as:

Being a polymer, a polyethylene glycol has a glass transitiontemperature (T_(g)) (which can be the same as or different from thesoftening point or the melt temperature of the polymer), as opposed to atrue melting point. Within in a certain range the glass transitiontemperature of a polyethylene glycol increases as its molecular weightincreases. For example PEG 400 has a T_(g) of 4-8° C., PEG 600 has aT_(g) of 20-25° C., PEG 1500 has a T_(g) of 44-48° C., PEG 4000 has aT_(g) of 54-58° C., and PEG 6000 has a T_(g) of 56-63° C. Poly(ethyleneglycol) is non-toxic, water soluble polymer used in a variety ofproducts. For example it is used in laxatives, skin creams andtoothpastes.

PEG-3350 [HO(C₂H₄O)_(n)] is a synthetic polyglycol having an averagemolecular weight of 3350.

What is needed therefore is a process for making an intraocular implantfrom a therapeutic agent and a polymer which does not result in or whichreduces the occurrence of undesirable therapeutic agent and/or polymerend products or crystalline forms of the therapeutic agent in theimplant.

SUMMARY

The present invention meets this need and provides a process for makingan intraocular implant comprising a therapeutic agent and a polymerwhich process does not result in or which reduces the occurrence ofundesirable therapeutic agent and/or polymer end products in theimplant. Additionally, the therapeutic agent is not present in theimplant in a crystalline form, so no polymorphs of the therapeutic agentare present in the implant. The present invention can meet this need byproviding a low temperature melt extrusion method for making an implantsuitable for intraocular use, the implant comprising a therapeutic agentand a suitable polymer.

The present processes provide extended and sustained release implantscomprising one or more ophthalmically active cyclic lipid therapeuticagents. Thus, the patient in whose eye the implant have been placedreceives a therapeutic amount of a cyclic lipid therapeutic agent for arelatively long or extended time period without requiring additionaladministrations of the agent or agents. The patient thereby has atherapeutically active agent available for treatment of the eye over arelatively long period of time, for example, on the order of at leastabout one week, such as between about two and about six months afteradministering the implant. Such extended release times facilitateobtaining successful treatment of ocular conditions. In addition,administering such implants preferably subconjunctivally can reduce theoccurrence and/or severity of at least one side effect, for example,hyperemia, relative to administering an identical amount of the cycliclipid therapeutic agent to the eye in the form of a topical composition.Further, subconjunctival administration of an implant comprising acyclic lipid therapeutic agent can be effective to provide a cycliclipid therapeutic agent to the retina to treat a retinal disease orcondition. As the subconjunctival administration of an implantcontaining a cyclic lipid therapeutic agent results in particularlyeffective delivery of such agents to the retina, the present inventionprovides a particularly advantageous method of delivering a cyclic lipidtherapeutic agent to ocular tissues without the side effects which canresult from systemic administration.

Implants in accordance with our invention comprise a cyclic lipidtherapeutic agent and a drug release sustaining component (such as asuitable polymer) associated with the cyclic lipid therapeutic agent. Inaccordance with the present invention, the cyclic lipid therapeuticagent can comprise, consists essentially of, or consists of aprostaglandin, prostaglandin analog, prostaglandin derivative,prostamide, prostamide analog, and a prostamide derivative that iseffective in treating an ocular condition, such as for example reducingor maintaining a reduced intraocular pressure in a hypertensive eye, orproviding to the retina of an eye an effective amount of a cyclic lipidtherapeutic agent having neuroprotective activities. The polymer isassociated with the cyclic lipid therapeutic agent to sustain release ofan amount of the cyclic lipid therapeutic agent into an eye in which theimplant is placed. The cyclic lipid therapeutic agent is released intothe eye for an extended period of time after the implant is areadministered, for example, subconjunctivally and is effective intreating or reducing at least one symptom of an ocular condition. Thepresent implants can relieve ocular hypertension by reducing theintraocular pressure of the eye or maintaining the intraocular pressureat a reduced level without substantial amounts of ocular hyperemia.Alternatively, the present implants can relieve disorders of theposterior segment of the eye, particularly, a retinal condition such asexudative or non-exudative age-related macular degeneration, bydelivering a cyclic lipid therapeutic agent via the sclera to thetissues of the posterior segment, in particular, the retina.

In one embodiment the implants comprise a cyclic lipid therapeutic agentand a biodegradable polymer matrix. The cyclic lipid therapeutic agentis associated with a biodegradable polymer matrix that releases drug ata rate effective to sustain release of an amount of the cyclic lipidtherapeutic agent from the implant effective to treat an ocularcondition. The implants can be biodegradable or bioerodible and providea sustained release of the cyclic lipid therapeutic agent to either orboth the anterior and posterior segments of the eye for extended periodsof time, such as for more than one week, for example for about threemonths or more and up to about six months or more.

The biodegradable polymer component of the implants can be a mixture ofbiodegradable polymers having a molecular weight between about 1000kiloDaltons (kD) and about 10 kD. For example, the biodegradable polymercan comprise a polylactic acid polymer having a molecular weight betweenabout 500 kD and about 50 kD, and preferably less than about 64kiloDaltons. Additionally or alternatively, the implants can comprise afirst biodegradable polymer of a polylactic acid, and a different secondbiodegradable polymer of a polylactic acid. Furthermore, the implantscan comprise a mixture of different biodegradable polymers, eachbiodegradable polymer having an inherent viscosity in a range of about0.2 deciliters/gram (dL/g) to about 1.0 dL/g.

The cyclic lipid therapeutic agent of the implants disclosed herein caninclude a prostaglandin, prostaglandin analog, prostaglandin derivative,prostamide, prostamide analog, or a prostamide derivative, that iseffective in treating ocular conditions. One example of a suitableprostamide derivative is bimatoprost. An embodiment of our invention isa sustained release bimatoprost implant, preferably implanted in thesubconjuntiva of the eye, to thereby remove the need for dailyadministration of the bimatoprost. The sustained release implant canprovide a controlled release of this hypotensive agent over an extendedperiod of time.

Other examples of cyclic lipid therapeutic agent within the scope of ourinvention include, without limitation, latanoprost, travoprost andunoprostone and salts derivatives, and analogs of these. In addition,the implant can be formulated with cyclic lipid therapeutic as well asone or more additional and different therapeutic agents that can beeffective to treat an ocular condition.

A process for making the present implants involves combining or mixingthe cyclic lipid therapeutic agent with a biodegradable polymer orpolymers. The mixture can then be extruded, compressed or solvent castto form a single composition. The single composition can then beprocessed to form an implant suitable for placement at an ocularlocation, such as for example at a subconjunctival, sub tenon,intravitreal or intrascleral location.

The implant can be placed in an ocular region such as, withoutlimitation, subconjunctivally, to treat a variety of ocular conditionsof the anterior or posterior segment. For example, the implant candeliver a cyclic lipid therapeutic agent to tissues of the anteriorsegment, thereby reducing ocular hypertension, and thus may be effectivein reducing at least one symptom of an ocular condition associated withan increased intraocular pressure. Alternatively, subconjunctivaladministration of the implant of the present invention can be effectiveto deliver the cyclic lipid therapeutic agent to the retina and othertissues of the posterior segment for the treatment of neurodegenerativeconditions such as age related macular degeneration (ARMD), such as“wet” or “dry” ARMD.

Our invention also encompasses the use of a cyclic lipid therapeuticagent and a polymeric component, as described herein, in the manufactureof a medicament for treating a patient.

Low Temperature Extrusion Processes Our invention encompasses a lowtemperature process for making an intraocular implant. The process iscarried out by combining a cyclic lipid therapeutic agent and a polymerto form a mixture. The mixture is then heated to a temperature betweenabout 50° C. and about 80° C., followed by extruding the heated mixtureto thereby make an implant suitable for intraocular use. By “lowtemperature” process is it meant a process which is carried out at atemperature between about 50° C. and about 80° C. The implant made bythis process is an intraocular implant, meaning that the implant isstructured and configured so as to be suitable for insertion orimplantation within an ocular tissue or within an ocular space orvirtual ocular space. Thus, an implant made by our process is suitablefor insertion or implantation into, for example, the anterior chamber,the posterior chamber, the vitreous cavity, the choroid, thesuprachoroidal space, the subretinal space, the conjunctiva, thesubconjunctival space, the episcleral space, the intracorneal space, theepicorneal space, the sclera, the pars plana, surgically-inducedavascular regions, the macula, the retina and sub-tenon locations.Preferably, when the implant contains an antihypertensive therapeuticagent (such as a prostaglandin analog, an alpha adrenergic receptoragonist or a beta blocker) the implant is implanted or insertedsubconjunctivally so as to be placed at a location proximate to thecilliary body, a target tissue for an antihypertensive therapeuticagent.

Because our low temperature process results in an implant suitable orintraocular use, therefore topical (i.e. as eye drops) and systemicroute of administrations are outside the scope of our invention.Additionally, the implants made by a process within the scope of ourinvention are not microparticles or microspheres (a microparticle ormicrosphere has a diameter of from about 0.1μ to about 5 microns) indiameter but are instead discrete solid body implants (from about 0.1 mmup to about 10 mm in diameter) intended for intraocular administrationas single, or as a small number (i.e. five or less) implants, as opposedto administration of a population of hundreds or thousands ofmicroparticles or microspheres.

In a low temperature process for making an intraocular implant with thescope of our invention the cyclic lipid therapeutic agent can be aprostaglandin, a prostaglandin analog, or and mixture thereof. Forexample, the cyclic lipid therapeutic agent can be bimatoprost, abimatoprost analog, latanoprost, a latanoprost analog, travoprost, atravoprost analog, unoprostone, a unoprostone analog, prostaglandin E1,a prostaglandin E1 analog, prostaglandin E2, a prostaglandin E2 analog,and mixtures thereof. A preferred cyclic lipid therapeutic agent withinthe scope of our invention is bimatoprost, a bimatoprost analog, andmixtures thereof.

The polymer matrix can be a biodegradable or a non-biodegradablepolymer. The biodegradable polymer can be for example a polylactic acid,polyglycolic acid, polylactide-co-glycolide, apoly(polylactide-co-glycolide) [PLGA] copolymer and copolymers thereof,as well as derivatives of these polymers. Other suitable polymers to usecan include poly caprolactones, and PLGA-PEG or PLA-PEG diblock ortriblock polymers.

In our low temperature process for making an intraocular implant, thepolymer can comprise from about 30% to about 95% by weight of theimplant and the cyclic lipid therapeutic agent can comprise from about5% to about 70% by weight of the implant. Notably, the potency of thecyclic lipid therapeutic agent released from the implant can be at leastabout 50% of its maximum potency.

A detailed embodiment of our low temperature process for making anintraocular implant can have the steps of: (a) combining a prostaglandinanalog and a biodegradable polymer to form a mixture; (b) heating themixture to a temperature between about 50° C. and about 80° C., and; (c)extruding the heated mixture, thereby making an implant suitable forintraocular use.

An alternate embodiment of our invention is a process for making anintraocular implant by firstly combining a cyclic lipid therapeuticagent, a first biodegradable polymer, and a second biodegradable polymerto form a mixture. Preferably, the first biodegradable polymer and thesecond biodegradable polymer are different polymers, the solubilities ofthe cyclic lipid therapeutic agent, the first biodegradable polymer, andthe second biodegradable polymer are substantially similar, and, themelting point of the second biodegradable polymer is lower than the melttemperature of the first biodegradable polymer. The next step in thisprocess is to heat the mixture made combining the cyclic lipidtherapeutic agent, the first biodegradable polymer, and a secondbiodegradable polymer. The mixture is heated to the temperature which islower than the melt temperature of the second biodegradable polymer.Advantageously, the temperature to which the mixture is heated is alsolower than the temperature at which the cyclic lipid therapeutic agentexhibits substantial degradation. The third step in this process is toextrude the heated mixture to thereby making an implant suitable forintraocular use.

In this alternate embodiment of our invention the first biodegradablepolymer can be for example a polylactic acid, polyglycolic acid,polylactide-co-glycolide, a poly(polylactide-co-glycolide) copolymer,and copolymers thereof. Additionally, the second biodegradable polymercan be any substituted poly lactide, poly glycolide, or poly(lactide-co-glycolide), any poly(caprolactone) or substituted derivativeor any of the above, as well as any of the above polymers where a lowmolecular weight polyether is incorporated as a block with the polymer.

Significantly, the second biodegradable polymer functions as a cosolventfor the first biodegradable polymer and for the cyclic lipid therapeuticagent. This permits a solid solution of these three components to beformed when the mixture is heated to the melt temperature of the secondbiodegradable polymer. The second biodegradable polymer has a low melttemperature (i.e. between about 50° C. about 80° C.) and importantly hasa solubility parameter which is similar to the solubility parameters ofboth the cyclic lipid therapeutic agent and the first biodegradablepolymer. In particular, suitable second biodegradable polymers caninclude:

Polymer Solubility Parameter (δ) decafluorobutane 10.6 Poly(isobutylene)16.2 Poly(hexemethylene Adipamide) 13.6 Poly Propylene 18.0 PolyEthylene 18.1 Poly Vinyl Chloride 21.4,as well as other low molecular weight polymers, waxes, and long chainhydrocarbons that have softening points below about 80° C. andsolubility parameters from about 12 to about 28 (MPa)^(1/2).

Preferably, the solubilities of the cyclic lipid therapeutic agent, thefirst biodegradable polymer, and the second biodegradable polymer areall within about 10 Mpa^(1/2) of each other. Additionally, thesolubility parameters (solubilities) of the cyclic lipid therapeuticagent, the first biodegradable polymer, and the second biodegradablepolymer are also preferably all within about 15 to 30 Mpa^(1/2).

The first biodegradable polymer can comprises from about 30% to about90% by weight of the implant, the second biodegradable polymer cancomprises from about 50% to about 30% by weight of the implant, and thecyclic lipid therapeutic agent can comprise from about 5% to about 30%by weight of the implant.

A detailed embodiment of this alternate embodiment of our invention is aprocess for making an intraocular implant, the process comprising thesteps of:

-   -   (a) combining:        -   (i) a prostaglandin analog, wherein the prostaglandin analog            comprises from about 5% to about 30% (and up to as much as            70%) by weight of the implant;        -   (ii) a poly(lactide-co-glycolide) copolymer, wherein the            poly(lactide-co-glycolide) comprises from about 30% to about            90% by weight of the implant. and;        -   (ii) a second biodegradable polymer to form a mixture,            wherein the second biodegradable polymer comprises from            about 5% to about 40% by weight of the implant, and wherein;            -   (α) the a poly(lactide-co-glycolide) copolymer and the                second biodegradable polymer are different polymers;            -   (β) the solubilities of the prostaglandin analog, the                poly(lactide-co-glycolide) copolymer, and the second                biodegradable polymer are all within about 10 Mpa^(1/2)                of each other, and;            -   (γ) the melt temperature of the second biodegradable                polymer is lower than the melt temperature of the a                poly(lactide-co-glycolide) copolymer, and is as well                lower than the temperature at which the prostaglandin                analog exhibits substantial degradation, or exhibits a                potency less than about 50% of it's label strength;    -   (b) heating the mixture to the lower melt temperature of the        second biodegradable polymer, so that the second biodegradable        polymer can function as a solvent for the prostaglandin analog        and for the a poly(lactide-co-glycolide) copolymer, and;    -   (c) extruding the heated mixture, thereby making an implant        suitable for intraocular use.

Our invention also encompasses a method for treating an ocular conditionusing an implant made as set forth herein. The implant can release (suchas release a therapeutically effective amount of) the cyclic lipidtherapeutic agent for at least about one week after its insertion orimplantation into an intraocular location. The cyclic lipid therapeuticagent can be a non-acid cyclic lipid therapeutic agent.

Importantly, the implant can have an average greatest dimension in arange of from about 0.4 mm to about 12 mm.

The cyclic lipid therapeutic agent can have the following formula (I)

wherein the dashed bonds represent a single or double bonds which can bein the cis or trans configuration, A is an alkyene or alkenylene radicalhaving from two to six carbon atoms, which radical may be interrupted byone or more oxide radicals and substituted with one or more hydroxy,oxo, alkoxy or alkycarboxyl groups wherein said alkyl radical comprisesfrom one to six carbon atoms; B is a cycloalkyl radical having fromthree to seven carbon atoms, or an aryl radical, selected from the groupconsisting of hydrocarbyl aryl and heteroaryl radicals having from fourto ten carbon atoms wherein the heteroatom is selected from the groupconsisting of nitrogen, oxygen and sulfur atoms; X is a radical selectedfrom the group consisting of hydrogen, a lower alkyl radical having fromone to six carbon atoms, R⁵—C(═O)— or R⁵—O—C(═O)— wherein R⁵ is a loweralkyl radical having from one to six carbon atoms; Z is ═O or represents2 hydrogen radicals; one of R₁ and R² is ═O, —OH or a —O—C(═O)—R⁶ group,and the other one is —OH or —O—C(═O)—R⁶, or R¹ is ═O and R² is H,wherein R⁶ is a saturated or unsaturated acyclic hydrocarbon grouphaving from 1 to about 20 carbon atoms, or —(CH₂)_(m)R⁷ wherein m is0-10, and R⁷ is cycloalkyl radical, having from three to seven carbonatoms, or a hydrocarbyl aryl or heteroaryl radical, as defined above, ora pharmaceutically acceptable salt thereof, provided however that when Bis not substituted with a pendant heteroatom-containing radical and Z is═O, then X is not —OR⁴.

Alternately, the cyclic lipid therapeutic agent can have the followingformula (II)

wherein y is 0 or 1, x is 0 or 1 and x+y re not both 1, Y is a radicalselected from the group consisting of alkyl, halo, nitro, amino, thiol,hydroxy, alkyloxy, alkylcarboxy and halo substituted alkyl, wherein saidalkyl radical comprises from one to six carbon atoms, n is O or aninteger of from 1 to 3 and R3 is ═O, —OH or —O—C(═O)R⁶.

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (III)

wherein hatched lines indicate the a configuration and solid trianglesindicate the 0 configuration.

Alternately, the cyclic lipid therapeutic agent can comprises a compoundhaving the following formula (IV)

wherein Y¹ is Cl or trifluoromethyl.

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (V)

and the 9- and/or 11- and/or 15-esters, thereof. Z can be O and X can beselected from the group consisting of NH₂ or OCH₃. Alternately, Y can be0, Z can be O and X can be selected from the group consisting of alkoxyand amido radicals.

Alternately, the cyclic lipid therapeutic agent comprises a compoundselected from the group consisting of:

-   -   a) cyclopentane        heptenol-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   b) cyclopentane        heptenamide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   c) cyclopentane N,        N-dimethylheptenamide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-penten-yl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   d) cyclopentane heptenyl        methoxide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3-,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   e) cyclopentane heptenyl        ethoxide-5-cis-2-(3α-hydroxy-4-meta-chloro-phenoxyl-1-trans-1-butenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   f) cyclopentane        heptenylamide-5-cis-2-(3α-hydroxy-4-meta-chloro-phenox-y-1-trans-butenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   g) cyclopentane        heptenylamide-5-cis-2-(3α-hydroxy-4-meta-tr-ifluoromethyl-phenoxy-1-trans-butenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   h) cyclopentane N-isopropyl        hepteneamide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   i) cyclopentane N-ethyl        heptenamide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   j) cyclopentane N-methyl        heptenamide-5-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   k) cyclopentane        heptenol-5-cis-2-(3α-hydroxy-4-meta-chlorophenoxy-1-trans-butenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α];    -   l) cyclopentane        heptenamide-5-cis-2-(3α-hydroxy-4-m-chlorophenoxy-1-trans-butenyl)-3,        5-dihydroxy, [1α, 2β, 3α, 5α], and    -   m) cyclopentane heptenol-5-cis-2-(3α-hydroxy-5-phenylpentyl)3,        5-dihydroxy, [1α, 2β, 3α, 5α].

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (VI)

wherein the dashed bonds represent a single or double bonds which can bein the cis or trans configuration, A is an alkyene or alkenylene radicalhaving from two to six carbon atoms, which radical may be interrupted byone or more oxide radicals and substituted with one or more hydroxy,oxo, alkoxy or alkycarboxyl groups wherein said alkyl radical comprisesfrom one to six carbon atoms; D is a branched or unbranched alkyl orheteroalkyl radical of from two to 10 carbon atoms, a cycloalkyl radicalhaving from three to seven carbon atoms, or an aryl radical, selectedfrom the group consisting of hydrocarbyl aryl and heteroaryl radicalshaving from four to ten carbon atoms wherein the heteroatom is selectedfrom the group consisting of nitrogen, oxygen and sulfur atoms; X is aradical selected from the group consisting of hydrogen, a lower alkylradical having from one to six carbon atoms, R⁵—C(═O)— or R⁵—O—C(═O)—wherein R⁵ is a lower alkyl radical having from one to six carbon atoms;Z is ═O or represents 2 hydrogen radicals; one of R₁ and R² is ═O, —OHor a —O—C(═O)—R⁶ group, and the other one is —OH or —O—C(═O)—R⁶, or R¹is ═O and R² is H, wherein R⁶ is a saturated or unsaturated acyclichydrocarbon group having from 1 to about 20 carbon atoms, or—(CH₂)_(m)R⁷ wherein m is 0-10, and R⁷ is cycloalkyl radical, havingfrom three to seven carbon atoms, or a hydrocarbyl aryl or heteroarylradical, as defined above, or a pharmaceutically acceptable saltthereof.

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (VII)

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (VIII)

wherein hatched lines indicate the α configuration and the solidtriangles comprise the β configuration.

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (IX)

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (X)

Alternately, the cyclic lipid therapeutic agent can comprise a compoundhaving the following formula (XI).

Additional aspects and advantages of the present invention are set forthin the following description and claims, particularly when considered inconjunction with the accompanying drawings.

DRAWINGS

The following drawings illustrate features and aspects of our invention.

FIG. 1 is a bar graph which shows the effect of decreasing temperature(the x axis) on the potency (the y axis) of the bimatoprost releasedfrom extruded implants made at different temperatures.

FIG. 2 is a graph which shows the total amount of bimatoprost released(the y-axis) over a period of fifty days (the x axis) from the FIG. 1extruded implant made at 57° C.

FIG. 3 is a graph which shows the daily amount of bimatoprost released(the y axis) from the FIG. 2 implant over a period of 50 days (the xaxis).

DESCRIPTION

Our invention is based on the discovery of a new process for makingsustained release intraocular implants. Implants made by our new processcan comprise a therapeutic agent and a polymer. The polymer functions asa carrier from which the therapeutic agent is released in vivo. Thetherapeutic agent and the polymer are heated and extruded to form animplant suitable for intraocular use. Preferably, the polymer has aT_(g) which is below the temperature at which the therapeutic agentloses a substantial amount (i.e. 50% or more) of its potency. If thepolymer (the first polymer) has a T_(g) which is above the temperatureat which the therapeutic agent loses a substantial amount of itspotency, the implant can be made by a process which entails adding acosolvent to an unheated mixture of the therapeutic agent and the firstpolymer. The cosolvent can also be a polymer (the second polymer).

The cosolvent must have two important properties. First the cosolventmust have a solubility (i.e. a solubility parameter) which is similar tothe solubilities (i.e. the solubility parameters) of both thetherapeutic agent and the first polymer. Clearly, this requires that thesolubility of the therapeutic agent be similar to the solubility of thefirst polymer. Upon selection of therapeutic agent, first polymer andcosolvent with similar solubilities, heating these three implantconstituents so as to melt the cosolvent will result in solubilizationof the therapeutic agent and the first polymer in the cosolvent.

The second important property of the co-solvent is that the co-solventhas a softening point which is below the temperature at which thetherapeutic agent loses a substantial amount of its potency. Thus, whenaccording to our process the therapeutic agent, the first polymer andthe co-solvent are mixed and then heated to the melt temperature of thecosolvent, the cosolvent solubilizes the therapeutic agent and the firstpolymer and does so without undue loss of potency of the therapeuticagent. Where the cosolvent is itself a polymer (the second polymer), thecosolvent solubilizes the therapeutic agent and the first polymer in theform of a solid solution.

A sustained release implant (implanted for example in the subconjuntiveof the eye) can remove the need for daily administration of ananti-hypertensive active agent by providing a controlled release of thehypotensive agent over an extended period of time. The antihypertensiveagent can be a prostaglandin analog, such as a bimatoprost. Abimatoprost containing polymeric implant can be an effective method ofdelivering a controlled dose of bimatoprost to the eye over an extendedtime. As described herein, controlled and sustained administration of atherapeutic agent through the subconjunctival administration of one ormore implants can be used to treat ocular conditions of the anteriorand/or posterior segment of the eye. The implants comprise apharmaceutically acceptable polymeric composition and are formulated torelease one or more pharmaceutically active agents, such as a cycliclipid, or other intraocular pressure lowering or neuroprotective agent,over an extended period of time. The implants are effective to provide atherapeutically effective dosage of the agent or agents to a region ofthe eye to treat or prevent one or more undesirable ocular conditions.Thus with a single implant administration cyclic lipid therapeuticagents can be made available at the site where they are needed and willbe maintained for an extended period of time, rather than subjecting thepatient to repeated injections or repeated administration of topicaldrops.

The implants of the present invention comprise a therapeutic componentand a drug release-sustaining component associated with the therapeuticcomponent. In accordance with the present invention, the therapeuticcomponent comprises, consists essentially of, or consists of, a cycliclipid therapeutic agent. The drug release sustaining component isassociated with the therapeutic component to sustain release of aneffective amount of the cyclic lipid therapeutic agent into an eye inwhich the implant is placed. The amount of the cyclic lipid therapeuticagent is released into the eye for a period of time greater than aboutone week after the implant is implanted or inserted in the eye of apatient, and is effective in treating or reducing a symptom of an ocularcondition, such as ocular hypertension or a retinal degeneration.

Definitions

“About” means that the number, range, value or parameter so qualifiedencompasses ten percent more and ten percent less of the number, range,value or parameter.

“Therapeutic component” means that portion of an implant other than thepolymer matrix comprising one or more therapeutic agents or substancesused to treat an ocular condition. The therapeutic component can be adiscrete region of an implant, or it may be homogenously distributedthroughout the implant. The therapeutic agents of the therapeuticcomponent comprise at least one cyclic lipid and are typicallyophthalmically acceptable, and are provided in a form that does notcause significant adverse reactions when the implant is placed in aneye.

“Cyclic lipid therapeutic agent” means that portion of an intraocularimplant which comprises one or more cyclic lipids having oculartherapeutic activity, including, without limitation, a prostaglandin,prostaglandin analog, prostaglandin derivative, prostamide, prostamideanalog, and a prostamide derivative that is effective in providing anophthalmic therapeutic effect, such as, without limitation, reducing ormaintaining a reduced intraocular pressure in a hypertensive eye, orproviding to the retina of an eye an effective amount of a cyclic lipidtherapeutic agent having neuroprotective activities. Cyclic lipidshaving anti-glaucoma activity can be identified by applying the cycliclipid to an eye with increased intraocular pressure, and evaluatingwhether the intraocular pressure decreases after the application. Cycliclipids having neuroprotective activity may be identified by, forexample, intravitreal administration of the cyclic lipid to an eyehaving a neurodegenerative disorder such as ARMD, and evaluating whetherthe neurodegeneration is slowed or halted, or whether visual acuity hasincreased.

“Drug release sustaining component” means that portion of an implantthat is effective to provide a sustained release of the therapeuticagents from the implant. A drug release sustaining component can be abiodegradable polymer matrix, or it can be a coating covering a coreregion of the implant that comprises a therapeutic component.

“Associated with” means mixed with, dispersed within, coupled to,covering, or surrounding.

“Ocular region” or “ocular site” means any area of the eyeball,including the anterior and posterior segment of the eye, and whichgenerally includes, but is not limited to, any functional (e.g., forvision) or structural tissues found in the eyeball, or tissues orcellular layers that partly or completely line the interior or exteriorof the eyeball. Specific examples of areas of the eyeball in an ocularregion include the anterior chamber, the posterior chamber, the vitreouscavity, the choroid, the suprachoroidal space, the conjunctiva, thesubconjunctival space, the episcleral space, the intracorneal space, theepicorneal space, the sclera, the pars plana, surgically-inducedavascular regions, the macula, and the retina.

“Ocular condition” means a disease, ailment or condition which affectsor involves the eye or one of the parts or regions of the eye. Broadlyspeaking the eye includes the eyeball and the tissues and fluids whichconstitute the eyeball, the periocular muscles (such as the oblique andrectus muscles) and the portion of the optic nerve which is within oradjacent to the eyeball. An anterior ocular condition is a disease,ailment or condition which affects or which involves an anterior (i.e.front of the eye) ocular region or site, such as a periocular muscle, aneye lid or an eye ball tissue or fluid which is located anterior to theposterior wall of the lens capsule or ciliary muscles. Thus, an anteriorocular condition primarily affects or involves the conjunctiva, thecornea, the anterior chamber, the iris, the posterior chamber (behindthe retina but in front of the posterior wall of the lens capsule), thelens or the lens capsule and blood vessels and nerve which vascularizeor innervate an anterior ocular region or site.

Thus, an anterior ocular condition can include a disease, ailment orcondition, such as for example, aphakia; pseudophakia; astigmatism;blepharospasm; cataract; conjunctival diseases; conjunctivitis; cornealdiseases; corneal ulcer; dry eye syndromes; eyelid diseases; lacrimalapparatus diseases; lacrimal duct obstruction; myopia; presbyopia; pupildisorders; refractive disorders and strabismus. Glaucoma can also beconsidered to be an anterior ocular condition because a clinical goal ofglaucoma treatment can be to reduce a hypertension of aqueous fluid inthe anterior chamber of the eye (i.e. reduce intraocular pressure).

A posterior ocular condition is a disease, ailment or condition whichprimarily affects or involves a posterior ocular region or site such aschoroid or sclera (in a position posterior to a plane through theposterior wall of the lens capsule), vitreous, vitreous chamber, retina,optic nerve (i.e. the optic disc), and blood vessels and nerves whichvascularize or innervate a posterior ocular region or site. Thus, aposterior ocular condition can include a disease, ailment or condition,such as for example, acute macular neuroretinopathy; Behcet's disease;choroidal neovascularization; diabetic uveitis; histoplasmosis;infections, such as fungal or viral-caused infections; maculardegeneration, such as acute macular degeneration, non-exudative agerelated macular degeneration and exudative age related maculardegeneration; edema, such as macular edema, cystoid macular edema anddiabetic macular edema; multifocal choroiditis; ocular trauma whichaffects a posterior ocular site or location; ocular tumors; retinaldisorders, such as central retinal vein occlusion, diabetic retinopathy(including proliferative diabetic retinopathy), proliferativevitreoretinopathy (PVR), retinal arterial occlusive disease, retinaldetachment, uveitic retinal disease; sympathetic opthalmia; VogtKoyanagi-Harada (VKH) syndrome; uveal diffusion; a posterior ocularcondition caused by or influenced by an ocular laser treatment;posterior ocular conditions caused by or influenced by a photodynamictherapy, photocoagulation, radiation retinopathy, epiretinal membranedisorders, branch retinal vein occlusion, anterior ischemic opticneuropathy, non-retinopathy diabetic retinal dysfunction, retinitispigmentosa, and glaucoma. Glaucoma can be considered a posterior ocularcondition because the therapeutic goal is to prevent the loss of orreduce the occurrence of loss of vision due to damage to or loss ofretinal cells or optic nerve cells (i.e. neuroprotection).

“Biodegradable polymer” means a polymer or polymers which degrade invivo, and wherein erosion of the polymer or polymers occurs concurrentwith or subsequent to release of the therapeutic agent. Specifically,hydrogels such as methylcellulose which act to release drug throughpolymer swelling are specifically excluded from the term “biodegradablepolymer”. The terms “biodegradable” and “bioerodible” are equivalent andare used interchangeably herein. A biodegradable polymer may be ahomopolymer, a copolymer, or a polymer comprising more than twodifferent polymeric units.

“Treat”, “treating”, or “treatment” means a reduction or resolution orprevention of an ocular condition, ocular injury or damage, or topromote healing of injured or damaged ocular tissue. A treatment isusually effective to reduce at least one symptom of an ocular condition,ocular injury or damage.

“Therapeutically effective amount” means the level or amount of agentneeded to treat an ocular condition, or reduce or prevent ocular injuryor damage without causing significant negative or adverse side effectsto the eye or a region of the eye. In view of the above, atherapeutically effective amount of a therapeutic agent, such as acyclic lipid, is an amount that is effective in reducing at least onesymptom of an ocular condition.

Implants have been developed which can release drug loads over varioustime periods. These implants when inserted into the subconjunctivalspace of an eye provide therapeutic levels of a cyclic lipid forextended periods of time (e.g., for about 1 week or more). The disclosedimplants are effective in treating ocular conditions, such as ocularconditions associated with elevated intraocular pressure, and morespecifically in reducing at least one symptom of glaucoma.

Processes for making implants have also been developed. For example, thepresent invention encompasses therapeutic polymeric implants andprocesses for making and using such implants. In one embodiment of thepresent invention, an implant comprises a biodegradable polymer matrix.The biodegradable polymer matrix is one type of a drug releasesustaining component. The biodegradable polymer matrix is effective informing a biodegradable implant. The biodegradable implant comprises acyclic lipid therapeutic agent associated with the biodegradable polymermatrix. The matrix degrades at a rate effective to sustain release of anamount of the cyclic lipid therapeutic agent for a time greater thanabout one week from the time in which the implant is placed in ocularregion or ocular site, such as the subconjunctival space of an eye.

The prostamide having a name cyclopentane N-ethylheptenamide-5-cis2-cis-2-(3α-hydroxy-5-phenyl-1-trans-pentenyl)-3,5-dihydroxy,[1α,2β,3α,5α] and derivatives, analods, and/or esters thereof, isparticularly preferred in this aspect of the invention. This compound isalso known as bimatoprost and is available in a topical ophthalmicsolution under the tradename, Lumigan® (Allergan, Inc., CA).

The Implant can comprise a therapeutic component which comprises,consists essentially of, or consists of bimatoprost, a salt thereof, ormixtures thereof. The cyclic lipid therapeutic agent can be in a liquid,derivatized, particulate, or powder form and it may be entrapped by thebiodegradable polymer matrix. Usually, cyclic lipid particles will havean effective average size less than about 3000 nanometers. In certainimplants, the particles may have an effective average particle sizeabout an order of magnitude smaller than 3000 nanometers. For example,the particles may have an effective average particle size of less thanabout 500 nanometers. In additional implants, the particles may have aneffective average particle size of less than about 400 nanometers, andin still further embodiments, a size less than about 200 nanometers.

The cyclic lipid therapeutic agent of the implant is preferably fromabout 10% to 90% by weight of the implant. More preferably, the cycliclipid therapeutic agent is from about 20% to about 80% by weight of theimplant. In a preferred embodiment, the cyclic lipid therapeutic agentcomprises about 20% by weight of the implant (e.g., 15%-25%). In anotherembodiment, the cyclic lipid therapeutic agent comprises about 50% byweight of the implant.

Suitable polymeric materials or compositions for use in the implantinclude those materials that are biocompatible with the eye so as tocause no substantial interference with the functioning or physiology ofthe eye. Such materials preferably are at least partially and morepreferably substantially completely biodegradable or bioerodible.

Examples of useful polymeric materials include, without limitation, suchmaterials derived from and/or including organic esters and organicethers, which when degraded result in physiologically acceptabledegradation products, including the monomers. Also, polymeric materialsderived from and/or including, anhydrides, amides, orthoesters and thelike, by themselves or in combination with other monomers, may also finduse. The polymeric materials may be addition or condensation polymers,advantageously condensation polymers. The polymeric materials may becross-linked or noncross-linked, for example not more than lightlycross-linked, such as less than about 5%, or less than about 1% of thepolymeric material being cross-linked. For the most part, besides carbonand hydrogen, the polymers will include at least one of oxygen andnitrogen, advantageously oxygen. The oxygen may be present as oxy, e.g.hydroxy or ether, carbonyl, e.g. nonoxo-carbonyl, such as carboxylicacid ester, and the like. The nitrogen may be present as amide, cyanoand amino. The polymers set forth in Heller, Biodegradable Polymers inControlled Drug Delivery, In: CRC Critical Reviews in Therapeutic DrugCarrier Systems, Vol. 1, CRC Press, Boca Raton, Fla. 1987, pp 39-90,which describes encapsulation for controlled drug delivery, may find usein the present implant.

Of additional interest are polymers of hydroxyaliphatic carboxylicacids, either homopolymers or copolymers, and polysaccharides.Polyesters of interest include polymers of D-lactic acid, L-lactic acid,racemic lactic acid, glycolic acid, polycaprolactone, and combinationsthereof. Generally, by employing the L-lactate or D-lactate, a slowlyeroding polymer or polymeric material is achieved, while erosion issubstantially enhanced with the lactate racemate.

Among the useful polysaccharides are, without limitation, calciumalginate, and functionalized celluloses, particularlycarboxymethylcellulose esters characterized by being water insoluble, amolecular weight of about 5 kD to 500 kD, for example. Other polymers ofinterest include, without limitation, polyvinyl alcohol, polyesters,polyethers and combinations thereof which are biocompatible and may bebiodegradable and/or bioerodible.

Some preferred characteristics of the polymers or polymeric materialsfor use in the present invention may include biocompatibility,compatibility with the therapeutic component, ease of use of the polymerin making the drug delivery systems of the present invention, ahalf-life in the physiological environment of at least about 6 hours,preferably greater than about one day, and water insolubility.

The biodegradable polymeric materials which are included to form thematrix are desirably subject to enzymatic or hydrolytic instability.Water soluble polymers may be cross-linked with hydrolytic orbiodegradable unstable cross-links to provide useful water insolublepolymers. The degree of stability can be varied widely, depending uponthe choice of monomer, whether a homopolymer or copolymer is employed,employing mixtures of polymers, and whether the polymer includesterminal acid groups.

Equally important to controlling the biodegradation of the polymer andhence the extended release profile of the implant is the relativeaverage molecular weight of the polymeric composition employed in theimplant. Different molecular weights of the same or different polymericcompositions may be included in the implant to modulate the releaseprofile. In certain implants, the relative average molecular weight ofthe polymer will range from about 9 to about 500 kD, usually from about10 to about 300 kD, and more usually from about 12 to about 100 kD.

In some implants copolymers of glycolic acid and lactic acid are used,where the rate of biodegradation is controlled by the ratio of glycolicacid to lactic acid. The most rapidly degraded copolymer has roughlyequal amounts of glycolic acid and lactic acid. Homopolymers, orcopolymers having ratios other than equal, are more resistant todegradation. The ratio of glycolic acid to lactic acid will also affectthe brittleness of the implant. The percentage of polylactic acid in thepolylactic acid polyglycolic acid (PLGA) copolymer can be 0-100%,preferably about 15-85%, more preferably about 35-65%. In some implantsa 50/50 PLGA copolymer is used.

The biodegradable polymer matrix of the subconjunctival implant cancomprise a mixture of two or more biodegradable polymers. For example,the implant can comprise a mixture of a first biodegradable polymer anda different second biodegradable polymer. One or more of thebiodegradable polymers can have terminal acid groups.

Release of a drug from an erodible polymer is the consequence of severalmechanisms or combinations of mechanisms. Some of these mechanismsinclude desorption from the implant's surface, dissolution, diffusionthrough porous channels of the hydrated polymer and erosion. Erosion canbe bulk or surface or a combination of both. As discussed herein, thematrix of the implant can release drug at a rate effective to sustainrelease of an amount of the prostamide component for more than one weekafter implantation into an eye. In certain implants therapeutic amountsof the cyclic lipid therapeutic agent are released for no more thanabout 30-35 days after administration to the subconjunctival space. Forexample, an implant may comprise bimatoprost, and the matrix of theimplant degrades at a rate effective to sustain release of atherapeutically effective amount of bimatoprost for about one monthafter being placed under the conjunctiva. As another example, theimplant may comprise bimatoprost, and the matrix releases drug at a rateeffective to sustain release of a therapeutically effective amount ofbimatoprost for more than forty days, such as for about six months.

One example of the biodegradable implant comprises a cyclic lipidtherapeutic agent associated with a biodegradable polymer matrix, whichcomprises a mixture of different biodegradable polymers. At least one ofthe biodegradable polymers is a polylactide having a molecular weight ofabout 63.3 kD. A second biodegradable polymer is a polylactide having amolecular weight of about 14 kD. Such a mixture is effective insustaining release of a therapeutically effective amount of the cycliclipid therapeutic agent for a time period greater than about one monthfrom the time the implant are placed administered under the conjuctiva.

Another example of a biodegradable implant comprises a cyclic lipidtherapeutic agent associated with a biodegradable polymer matrix, whichcomprises a mixture of different biodegradable polymers, eachbiodegradable polymer having an inherent viscosity from about 0.16 dL/gto about 1.0 dL/g. For example, one of the biodegradable polymers mayhave an inherent viscosity of about 0.3 dl/g. A second biodegradablepolymer may have an inherent viscosity of about 1.0 dl/g. Additionalimplant may comprise biodegradable polymers that have an inherentviscosity between about 0.2 dl/g and 0.5 dl/g. The inherent viscositiesidentified above may be determined in chloroform, 0.1% at 25° C.

One particular implant formulation comprises bimatoprost associated witha combination of two different polylactide polymers. The bimatoprost ispresent in about 20% by weight of the implant. One polylactide polymerhas a molecular weight of about 14 kD and an inherent viscosity of about0.3 dl/g, and the other polylactide polymer has a molecular weight ofabout 63.3 kD and an inherent viscosity of about 1.0 dl/g. The twopolylactide polymers are present in the implant in a 1:1 ratio. Such animplant may be effective in releasing the bimatoprost for more than twomonths.

The release of the cyclic lipid therapeutic agent from the implant intothe subconjuctiva can include an initial burst of release followed by agradual increase in the amount of the cyclic lipid therapeutic agentreleased, or the release can include an initial delay in release of theprostamide component followed by an increase in release. When theimplant is substantially completely degraded, the percent of the cycliclipid therapeutic agent that has been released is about one hundred. Theimplant disclosed herein do not completely release, or release about100% of the cyclic lipid therapeutic agent, until after about one weekof being placed in an eye.

It can be desirable to provide a relatively constant rate of release ofthe cyclic lipid therapeutic agent from the implant over the life of theimplant. For example, it may be desirable for the cyclic lipidtherapeutic agent to be released in amounts from about 0.01 μg to about2 μg per day for the life of the implant. However, the release rate canchange to either increase or decrease depending on the formulation ofthe biodegradable polymer matrix. In addition, the release profile ofthe prostamide component may include one or more linear portions and/orone or more non-linear portions. Preferably, the release rate is greaterthan zero once the implant has begun to degrade or erode.

The implant can be monolithic, i.e. having the active agent or agentshomogenously distributed through the polymeric matrix, or encapsulated,where a reservoir of active agent is encapsulated by the polymericmatrix. Due to ease of manufacture, monolithic implants are usuallypreferred over encapsulated forms. However, the greater control affordedby the encapsulated implant may be of benefit in some circumstances,where the therapeutic level of the drug falls within a narrow window. Inaddition, the therapeutic component, including the cyclic lipidtherapeutic agent, can be distributed in a non-homogenous pattern in thematrix. For example, the implant may include a portion that has agreater concentration of the cyclic lipid therapeutic agent relative toa second portion of the implant.

The implants disclosed herein can have a size of between about 0.1 mmand about 12 mm. For needle (syringe)-injected implant, the implant canhave any appropriate dimensions so long as the longest dimension of theimplant permits the implant to move through a canula of the needle. Thisis generally not a problem in the administration of implant. Thesubconjunctival space in humans is able to accommodate relatively largevolumes of implant.

The total weight of an implant is from about 0.1 mg to about 5 mg. Forexample, a single subconjunctival implant (human patient) can weighbetween 0.1 to 2 mg, including the incorporated therapeutic component.The dosage of the therapeutic component in the implant is generally inthe range of from about 55% to about 95% by weight of the implantweight. Thus, implant can be prepared where the center may be of onematerial and the surface may have one or more layers of the same or adifferent composition, where the layers may be cross-linked, or of adifferent molecular weight, different density or porosity, or the like.For example, where it is desirable to quickly release an initial bolusof drug, the center of the implant may be a polylactate coated with apolylactate-polyglycolate copolymer, so as to enhance the rate ofinitial degradation. Alternatively, the center may be polyvinyl alcoholcoated with polylactate, so that upon degradation of the polylactateexterior the center would dissolve and be rapidly washed out of the eye.

The implant can be of any geometry (excluding microspheres andmicroparticles). The upper limit for the implant size will be determinedby factors such as toleration for the implant, size limitations oninsertion, desired rate of release, ease of handling, etc. The size andform of the implant can also be used to control the rate of release,period of treatment, and drug concentration at the site of implantation.Larger implants will deliver a proportionately larger dose, butdepending on the surface to mass ratio, may have a slower release rate.The particular size and geometry of the implant are chosen to suit theactivity of the active agent and the location of its target tissue.

The proportions of the cyclic lipid therapeutic agent, polymer, and anyother modifiers can be empirically determined by formulating severalimplants with varying average proportions. A USP approved method fordissolution or release test can be used to measure the rate of release.For example, using an infinite sink method, a weighed sample of theimplant is added to a measured volume of a solution containing 0.01Mphosphate buffered saline (PBS) pH 7.4 at 37° C., where the solutionvolume will be such that the drug concentration is after release is lessthan 5% of saturation. The mixture is maintained at 37° C. and stirredslowly to maintain the implant in suspension. The appearance of thedissolved drug as a function of time may be followed by various methodsknown in the art, such as spectrophotometrically, HPLC, massspectroscopy, etc. until the absorbance becomes constant or untilgreater than 90% of the drug has been released.

In addition to the cyclic lipid therapeutic agent included in theimplant disclosed herein, the implant can also include one or moreadditional ophthalmically acceptable therapeutic agents. For example,the implant can include one or more antihistamines, one or moreantibiotics, one or more beta blockers, one or more steroids, one ormore antineoplastic agents, one or more immunosuppressive agents, one ormore antiviral agents, one or more antioxidant agents, and mixturesthereof. Additional pharmacologic or therapeutic agents which may finduse in the present systems, include, without limitation, those disclosedin U.S. Pat. No. 4,474,451, columns 4-6 and U.S. Pat. No. 4,327,725,columns 7-8.

Examples of antihistamines include, and are not limited to, loradatine,hydroxyzine, diphenhydramine, chlorpheniramine, brompheniramine,cyproheptadine, terfenadine, clemastine, triprolidine, carbinoxamine,diphenylpyraline, phenindamine, azatadine, tripelennamine,dexchlorpheniramine, dexbrompheniramine, methdilazine, and trimprazinedoxylamine, pheniramine, pyrilamine, chiorcyclizine, thonzylamine, andderivatives thereof.

Examples of antibiotics include without limitation, cefazolin,cephradine, cefaclor, cephapirin, ceftizoxime, cefoperazone, cefotetan,cefutoxime, cefotaxime, cefadroxil, ceftazidime, cephalexin,cephalothin, cefamandole, cefoxitin, cefonicid, ceforanide, ceftriaxone,cefadroxil, cephradine, cefuroxime, ampicillin, amoxicillin,cyclacillin, ampicillin, penicillin G, penicillin V potassium,piperacillin, oxacillin, bacampicillin, cloxacillin, ticarcillin,azlocillin, carbenicillin, methicillin, nafcillin, erythromycin,tetracycline, doxycycline, minocycline, aztreonam, chloramphenicol,ciprofloxacin hydrochloride, clindamycin, metronidazole, gentamicin,lincomycin, tobramycin, vancomycin, polymyxin B sulfate, colistimethate,colistin, azithromycin, augmentin, sulfamethoxazole, trimethoprim, andderivatives thereof.

Examples of beta blockers include acebutolol, atenolol, labetalol,metoprolol, propranolol, timolol, and derivatives thereof. Examples ofsteroids include corticosteroids, such as cortisone, prednisolone,flurometholone, dexamethasone, medrysone, loteprednol, fluazacort,hydrocortisone, prednisone, betamethasone, prednisone,methylprednisolone, riamcinolone hexacatonide, paramethasone acetate,diflorasone, fluocinonide, fluocinolone, triamcinolone, derivativesthereof, and mixtures thereof.

Examples of antineoplastic agents include adriamycin, cyclophosphamide,actinomycin, bleomycin, duanorubicin, doxorubicin, epirubicin,mitomycin, methotrexate, fluorouracil, carboplatin, carmustine (BCNU),methyl-CCNU, cisplatin, etoposide, interferons, camptothecin andderivatives thereof, phenesterine, taxol and derivatives thereof,taxotere and derivatives thereof, vinblastine, vincristine, tamoxifen,etoposide, piposulfan, cyclophosphamide, and flutamide, and derivativesthereof.

Examples of immunosuppressive agents include cyclosporine, azathioprine,tacrolimus, and derivatives thereof. Examples of antiviral agentsinclude interferon gamma, zidovudine, amantadine hydrochloride,ribavirin, acyclovir, valciclovir, dideoxycytidine, phosphonoformicacid, ganciclovir, and derivatives thereof.

Examples of antioxidant agents include ascorbate, alpha-tocopherol,mannitol, reduced glutathione, various carotenoids, cysteine, uric acid,taurine, tyrosine, superoxide dismutase, lutein, zeaxanthin,cryotpxanthin, astazanthin, lycopene, N-acetyl-cysteine, carnosine,gamma-glutamylcysteine, quercitin, lactoferrin, dihydrolipoic acid,citrate, Ginkgo Biloba extract, tea catechins, bilberry extract,vitamins E or esters of vitamin E, retinyl palmitate, and derivativesthereof.

Other therapeutic agents include squalamine, carbonic anhydraseinhibitors, alpha-2 adrenergic receptor agonists, antiparasitics,antifungals, and derivatives thereof. The amount of active agent oragents employed in the implant, individually or in combination, willvary widely depending on the effective dosage required and the desiredrate of release from the implant. Usually the agent will be at leastabout 1, more usually at least about 10 weight percent of the implant,and usually not more than about 80, more usually not more than about 40weight percent of the implant.

Some of the present implants may comprise a cyclic lipid therapeuticagent that comprises a combination of two or more different cyclic lipidderivatives. One implant or dosage of implant may comprise a combinationof bimatoprost and latanoprost. Another implant or dosage of implant maycomprise a combination of bimatoprost and travoprost.

As discussed herein, the present implant can comprise additionaltherapeutic agents. For example, one implant or dosage of implant maycomprise a combination of bimatoprost and a beta-adrenergic receptorantagonist. More specifically, the implant or dosage of implant maycomprise a combination of bimatoprost and Timolol®. Or, an implant ordosage of implant may comprise a combination of bimatoprost and acarbonic anyhdrase inhibitor. For example, the implant or dosage ofimplant may comprise a combination of bimatoprost and dorzolamide(Trusopt®).

In addition to the therapeutic component, the implant disclosed hereincan include or may be provided in compositions that include effectiveamounts of buffering agents, preservatives and the like. Suitable watersoluble buffering agents include, without limitation, alkali andalkaline earth carbonates, phosphates, bicarbonates, citrates, borates,acetates, succinates and the like, such as sodium phosphate, citrate,borate, acetate, bicarbonate, carbonate and the like. These agentsadvantageously present in amounts sufficient to maintain a pH of thesystem of between about 2 to about 9 and more preferably about 4 toabout 8. As such the buffering agent may be as much as about 5% byweight of the total implant. Suitable water soluble preservativesinclude sodium bisulfite, sodium bisulfate, sodium thiosulfate,ascorbate, benzalkonium chloride, chlorobutanol, thimerosal,phenylmercuric acetate, phenylmercuric borate, phenylmercuric nitrate,parabens, methylparaben, polyvinyl alcohol, benzyl alcohol,phenylethanol and the like and mixtures thereof. These agents may bepresent in amounts of from about 0.001% to about 5% by weight andpreferably about 0.01% to about 2% by weight. In at least one of thepresent implant, a benzylalkonium chloride preservative is provided inthe implant, such as when the cyclic lipid therapeutic agent consistsessentially of bimatoprost.

In some situations several implants can be implanted or inserted, eachemploying the same or different pharmacological agents. In this way, acocktail of release profiles, giving a biphasic or triphasic releasewith a single administration is achieved, where the pattern of releasemay be greatly varied.

Additionally, release modulators such as those described in U.S. Pat.No. 5,869,079 may be included in the implant. The amount of releasemodulator employed will be dependent on the desired release profile, theactivity of the modulator, and on the release profile of the cycliclipid therapeutic agent in the absence of modulator. Electrolytes suchas sodium chloride and potassium chloride may also be included in theimplant. Where the buffering agent or enhancer is hydrophilic, it mayalso act as a release accelerator. Hydrophilic additives act to increasethe release rates through faster dissolution of the material surroundingthe drug in the implant, which increases the surface area of the drugexposed, thereby increasing the rate of drug bioerosion. Similarly, ahydrophobic buffering agent or enhancer dissolves more slowly, slowingthe exposure of drug, and thereby slowing the rate of drug bioerosion.

In certain implants the combination of bimatoprost and a biodegradablepolymer matrix is released or delivered an amount of bimatoprost betweenabout 0.1 mg to about 0.5 mg for about 3-6 months after implantationinto the eye. Various techniques can be employed to produce the implantsdescribed herein. Useful techniques include, but are not necessarilylimited to, grinding methods, compression methods, extrusion methods,interfacial methods, molding methods, injection molding methods,combinations thereof and the like.

Compression methods can be used to make the implants, and typicallyyield implants with faster release rates than extrusion methods.Compression methods may use pressures of about 50-150 psi, morepreferably about 70-80 psi, even more preferably about 76 psi, and usetemperatures of about 0 degrees C. to about 115 degrees C., morepreferably about 25 degrees C.

In one embodiment, a method for producing therapeutic polymeric implantcomprises encapsulating a cyclic lipid therapeutic agent with apolymeric component to form a cyclic lipid-encapsulated implant. Suchimplant are effective in treating one or more ocular conditions, asdescribed herein, and are suitable for administration to a patient intothe subconjunctival space. The therapeutic activity of the cyclic lipidtherapeutic agent remains stable during storage of the implant which maybe attributed to the particular encapsulated form of the implant.

As discussed herein, the cyclic lipid therapeutic agent can comprises asingle type of cyclic lipid derivative or derivatives. In certainembodiments, the cyclic lipid therapeutic agent comprises at least oneprostamide derivative selected from the group consisting of bimatoprost,esters thereof, and mixtures thereof. In a further embodiment, thecyclic lipid therapeutic agent consists essentially of bimatoprost.

In additional embodiments, the cyclic lipid therapeutic agent cancomprise combinations of two or more different cyclic lipid derivatives,such as a combination of bimatoprost and latanoprost, bimatoprost andtravoprost, and the like.

The present methods are effective in producing encapsulated cyclic lipidtherapeutic agent implant that maintain or preserve a substantialportion, if not all, of the therapeutic activity after a terminalsterilization procedure. It can be understood, that the present methodsmay also comprise a step of terminally sterilizing the implant. Theimplant can be sterilized before packaging or in their packaging.Sterilization of packages containing the present implant or implants isoften preferred. The method may comprise exposing the present implant orimplants to sterilizing amounts of gamma radiation, e-beam radiation,and other terminal sterilization products. In one embodiment, a methodmay comprise a step of exposing the present implant to gamma radiationat a dose of about 25 kGy.

As discussed herein, the polymeric component used in the present methodcan comprise a biodegradable polymer or biodegradable copolymer. In atleast one embodiment, the polymeric component comprises a poly(lactide-co-glycolide) PLGA copolymer. In a further embodiment, the PLGAcopolymer has a lactide/glycolide ratio of 75/25. In a still furtherembodiment, the PLGA copolymer has at least one of a molecular weight ofabout 63 kilodaltons and an inherent viscosity of about 0.6 dL/g.

The present methods may also comprise a step of forming a firstcomposition which comprises a cyclic lipid therapeutic agent, apolymeric component, and an organic solvent, and a step of forming asecond oil-containing composition, and mixing the first composition andthe second oil-containing composition.

The rate at which an implant degrades can vary, as discussed herein, andtherefore, the present implant can release the cyclic lipid therapeuticagent for different periods of time depending on the particularconfiguration and materials of the implant. In at least one embodiment,an implant can release about 1% of the cyclic lipid therapeutic agent inthe implant per day. In a further embodiment, the implant may have arelease rate of about 0.7% per day when measured in vitro. Thus, over aperiod of about 40 days, about 30% of the cyclic lipid therapeutic agentmay have been released.

As discussed herein, the amount of the cyclic lipid therapeutic agentpresent in the implant can vary. In certain embodiments, about 50% wt/wtof the implant is the cyclic lipid therapeutic agent. In furtherembodiments, the cyclic lipid therapeutic agent constitutes about 40%wt/wt of the implant.

The implant of the present invention can be inserted into thesubconjunctival space of an eye by a variety of methods. The method ofplacement can influence the therapeutic component or drug-releasekinetics. A preferred means of administration of the implant of thepresent invention is by subconjunctival injection. The location of thesite of injection of the implant may influence the concentrationgradients of therapeutic component or drug surrounding the element, andthus influence the delivery rate to a given tissue of the eye. Forexample, an injection into the conjunctiva toward the posterior of theeye will direct drug more efficiently to the tissues of the posteriorsegment, while a site of injection closer to the anterior of the eye(but avoiding the cornea) may direct drug more efficiently to theanterior segment.

The Implant can be administered to patients by administering anophthalmically acceptable composition which comprises the implant to thepatient. For example, implant may be provided in a liquid composition, asuspension, an emulsion, and the like, and administered by injection orimplantation into the subconjunctival space of the eye.

The present implants or implant are configured to release an amount ofcyclic lipid therapeutic agent effective to treat an ocular condition,such as by reducing at least one symptom of the ocular condition. Morespecifically, the implant may be used in a method to treat glaucoma,such as open angle glaucoma, ocular hypertension, chronic angle-closureglaucoma, with patent iridotomy, psuedoexfoliative glaucoma, andpigmentary glaucoma. By injecting the cyclic lipid therapeuticagent-containing implant into the subconjunctival space of an eye, it isbelieved that the cyclic lipid therapeutic agent is effective to enhanceaqueous humor flow thereby reducing intraocular pressure. Additionally,subconjunctival delivery of implant containing a cyclic lipidtherapeutic agent can to provide a therapeutic concentrations of thetherapeutic agent to the retina of the eye.

The implants disclosed herein can be used to prevent or to treat variousocular diseases or conditions, including the following:maculopathies/retinal degeneration: macular degeneration, including agerelated macular degeneration (ARMD), such as non-exudative age relatedmacular degeneration and exudative age related macular degeneration,choroidal neovascularization, retinopathy, including diabeticretinopathy, acute and chronic macular neuroretinopathy, central serouschorioretinopathy, and macular edema, including cystoid macular edema,and diabetic macular edema. Uveitis/retinitis/choroiditis: acutemultifocal placoid pigment epitheliopathy, Behcet's disease, birdshotretinochoroidopathy, infectious (syphilis, lyme, tuberculosis,toxoplasmosis), uveitis, including intermediate uveitis (pars planitis)and anterior uveitis, multifocal choroiditis, multiple evanescent whitedot syndrome (MEWDS), ocular sarcoidosis, posterior scleritis,serpignous choroiditis, subretinal fibrosis, uveitis syndrome, andVogt-Koyanagi-Harada syndrome. Vascular diseases/exudative diseases:retinal arterial occlusive disease, central retinal vein occlusion,disseminated intravascular coagulopathy, branch retinal vein occlusion,hypertensive fundus changes, ocular ischemic syndrome, retinal arterialmicroaneurysms, Coat's disease, parafoveal telangiectasis, hemi-retinalvein occlusion, papillophlebitis, central retinal artery occlusion,branch retinal artery occlusion, carotid artery disease (CAD), frostedbranch angitis, sickle cell retinopathy and other hemoglobinopathies,angioid streaks, familial exudative vitreoretinopathy, Eales disease.Traumatic/surgical: sympathetic ophthalmia, uveitic retinal disease,retinal detachment, trauma, laser, PDT, photocoagulation, hypoperfusionduring surgery, radiation retinopathy, bone marrow transplantretinopathy. Proliferative disorders: proliferative vitreal retinopathyand epiretinal membranes, proliferative diabetic retinopathy. Infectiousdisorders: ocular histoplasmosis, ocular toxocariasis, presumed ocularhistoplasmosis syndrome (PONS), endophthalmitis, toxoplasmosis, retinaldiseases associated with HIV infection, choroidal disease associatedwith HIV infection, uveitic disease associated with HIV Infection, viralretinitis, acute retinal necrosis, progressive outer retinal necrosis,fungal retinal diseases, ocular syphilis, ocular tuberculosis, diffuseunilateral subacute neuroretinitis, and myiasis. Genetic disorders:retinitis pigmentosa, systemic disorders with associated retinaldystrophies, congenital stationary night blindness, cone dystrophies,Stargardt's disease and fundus flavimaculatus, Best's disease, patterndystrophy of the retinal pigmented epithelium, X-linked retinoschisis,Sorsby's fundus dystrophy, benign concentric maculopathy, Bietti'scrystalline dystrophy, pseudoxanthoma elasticum. Retinal tears/holes:retinal detachment, macular hole, giant retinal tear. Tumors: retinaldisease associated with tumors, congenital hypertrophy of the RPE,posterior uveal melanoma, choroidal hemangioma, choroidal osteoma,choroidal metastasis, combined hamartoma of the retina and retinalpigmented epithelium, retinoblastoma, vasoproliferative tumors of theocular fundus, retinal astrocytoma, intraocular lymphoid tumors.Miscellaneous: punctate inner choroidopathy, acute posterior multifocalplacoid pigment epitheliopathy, myopic retinal degeneration, acuteretinal pigment epithelitis and the like.

In at least one embodiment, a method of reducing intraocular pressure inan eye of a patient comprises administering an implant containing acyclic lipid therapeutic agent, as disclosed herein, to a patient bysubconjuctival injection. A syringe apparatus including an appropriatelysized needle, for example, a 22 gauge needle, a 27 gauge needle or a 30gauge needle, can be effectively used to inject the composition withinto the subconjunctival space of an eye of a human or animal. Frequentrepeat injections are often not necessary due to the extended release ofthe cyclic lipid therapeutic agent from the implant.

In certain implants, the implant preparation comprises a therapeuticcomponent which consists essentially of bimatoprost, salts thereof, andmixtures thereof, and a biodegradable polymer matrix. The biodegradablepolymer matrix can consist essentially of PLA, PLGA, or a combinationthereof. When placed in the eye, the preparation releases about 40% toabout 60% of the bimatoprost to provide a loading dose of thebimatoprost within about one day after subconjunctival administration.Subsequently, the implant release about 1% to about 2% of thebimatoprost per day to provide a sustained therapeutic effect. Suchimplant preparations may be effective in reducing and maintaining areduced intraocular pressure, such as below about 15 mm Hg for severalmonths, and potentially for one or two years.

Other implants disclosed herein can be configured such that the amountof the cyclic lipid therapeutic agent that is released from the implantwithin two days of subconjunctival injection is less than about 40% ofthe total amount of the cyclic lipid therapeutic agent in the implant.In certain formulations, 40% of the cyclic lipid therapeutic agent isnot released until after about one week of injection. In certain implantformulations, less than about 30% of the cyclic lipid therapeutic agentis released within about one day of placement in the eye, and about 2%of the remainder is released for about 1 month after being placed in theeye. In another implant, less than about 20% of the cyclic lipidtherapeutic agent is released within about one day of subconjunctivaladministration, and about 1% is released for about 2 months after suchadministration.

EXAMPLES

The following illustrative examples and are not intended to limit thescope of our invention.

Example 1

Method for Making Bimatoprost Microparticles

Biodegradable microparticles (microspheres) suitable for intraocular usewere made by combining bimatoprost with a biodegradable polymer. Thus800 mg of polylactic acid (PLA) was combined with 200 mg of bimatoprost.The combination was dissolved in 25 milliliters of dichloromethane. Themixture was then placed in a vacuum at 45° C. overnight to evaporate thedichloromethane. The resulting mixture was in the form of a cast sheet.The cast sheet was cut and ground in a high shear grinder with dry iceuntil the particles could pass through a sieve having a pore size ofabout 125 μm. The percent of bimatoprost present in the microparticleswas analyzed using high pressure liquid chromatography (HPLC). Thepercent release of bimatoprost from the microparticles was profiledusing dialysis. The percent of bimatoprost remaining in the recoveredparticles was analyzed by HPLC.

The release profile obtained is as shown in Table 1.

TABLE 1 Elapsed Time Time Point (Days) Percent Released Percent Per DayStart 0 — — 1 1.03 47.51 47.51 2 2.03 47.92 0.41 3 3.03 49.99 2.07 44.03 50.09 0.10 5 7.04 50.90 0.82

The percent loading of bimatoprost was 14.93%. The percent ofbimatoprost remaining in the recovered release particles was 4.94%.

Example 2

Extrusion and Compression Processes for Making Bimatoprost Implants

Bimatoprost is combined with a biodegradable polymer composition in amortar. The combination is mixed with a shaker set at about 96 RPM forabout 15 minutes. The powder blend is scraped off the wall of the mortarand is then remixed for an additional 15 minutes. The mixed powder blendis heated to a semi-molten state at specified temperature for a total of30 minutes, forming a polymer/drug melt.

Rods are manufactured by pelletizing the polymer/drug melt using a 9gauge polytetrafluoroethylene (PTFE) tubing, loading the pellet into thebarrel and extruding the material at the specified core extrusiontemperature into filaments. The filaments are then cut into about 1 mgsize implants or drug delivery systems. The rods may have dimensions ofabout 2 mm long×0.72 mm diameter. The rod implants weigh between about900 μg and 1100 μg.

Wafers are formed by flattening the polymer melt with a Carver press ata specified temperature and cutting the flattened material into wafers,each weighing about 1 mg. The wafers have a diameter of about 2.5 mm anda thickness of about 0.13 mm. The wafer implants weigh between about 900μg and 1100 μg.

In-vitro release testing is performed by placing each implant into a24-mL screw cap vial with 10 mL of Phosphate Buffered Saline solution at37° C. 1 mL aliquots are removed and are replaced with equal volume offresh medium on day 1, 4, 7, 14, 28, and every two weeks thereafter.

Drug assays are performed by HPLC, which consists of a Waters 2690Separation Module (or 2695), and a Waters 996 Photodiode Array Detector.An Ultrasphere, C-18 (2), 5 μm; 4.6×150 mm column at 30° C. is used forseparation and the detector is set at about 264 nm. The mobile phase is(10:90) MeOH—buffered mobile phase with a flow rate of 1 mL/min and atotal run time of 12 min per sample. The buffered mobile phase maycomprise (68:0.75:0.25:31) 13 mM 1-Heptane Sulfonic Acid, sodiumsalt—glacial acetic acid—triethylamine—Methanol. The release rates aredetermined by calculating the amount of drug being released in a givenvolume of medium over time in μg/day.

Polymers which may be used in the implants can be obtained fromBoehringer Ingelheim. Examples of polymer include: RG502, RG502H, RG752,R202H, R203 and R206, and Purac PDLG (50/50). RG502 and RG502H are(50:50) poly(D,L-lactide-co-glycolide) with RG502 having an ester endgroup and RG502H having an acid end group, RG752 is (75:25)poly(D,L-lactide-co-glycolide), R202H is 100% poly(D, L-lactide) withacid end group or terminal acid groups, R203 and R206 are both 100%poly(D, L-lactide). Purac PDLG (50/50) is (50:50)poly(D,L-lactide-co-glycolide). The inherent viscosity of RG502, RG502H,RG752, R202H, R203, R206, and Purac PDLG are 0.2, 0.2, 0.2, 0.2, 0.3,1.0, and 0.2 dL/g, respectively. The average molecular weight of RG502,RG502H, RG752, R202H, R203, R206, and Purac PDLG are, 11700, 11200,11200, 6500, 14000, 63300, and 9700 daltons, respectively. The implantsmade can be suitable for intraocular use to treat an ocular condition.

Example 3

Bimatoprost/PLA/PLGA Intraocular Implants for Treating Glaucoma

A 72 year old female suffering from glaucoma in both eyes receives anintraocular implant containing bimatoprost and a combination of a PLAand PLGA in each eye. The implants weigh about 1 mg, and contain about500 mg of bimatoprost. One implant is placed in the vitreous of each eyeusing a syringe. In about two days, the patient reports a substantialrelief in ocular comfort. Examination reveals that the intraocularpressure has decreased: the average intraocular pressure measured at8:00 AM has decreased from 28 mm Hg to 14.3 mm Hg. The patient ismonitored monthly for about 6 months. Intraocular pressure levels remainbelow 15 mm Hg for six months, and the patient reports reduced oculardiscomfort.

Example 4

Bimatoprost/PLA Intraocular Implants for Treating Ocular Hypertension

A 62 year old male presents with an intraocular pressure in his left eyeof 33 mm Hg. An implant containing 400 mg of bimatoprost and 600 mg ofPLA is inserted into the vitreous of the left eye using a trocar. Thepatient's intraocular pressure is monitored daily for one week, and thenmonthly thereafter. One day after implantation, the intraocular pressureis reduced to 18 mm Hg. By day 7 after implantation, the intraocularpressure is relatively stable at 14 mm Hg. The patient does notexperience any further signs of elevated intraocular pressure for 2years.

Example 5

Low Temperature Melt Extrusion Process for Making Bimatoprost Implants

The prostamide analog bimatoprost((Z)-7-[1R,2R,3R,5S)-3,5-Dihydoxy-2-[1E,3S)-3-hydroxy-5-phenyl-1-pentenyl]cyclopentyl]-5-N-ethylheptenamide)was incorporated into sustained release polymeric implants made by a lowtemperature (65° to 71° C.) melt extrusion process. The implants madecomprised from 30 wt % to 50 wt % bimatoprost and from 50 wt % to 70 wt% poly (D,L,-lactide-co-glycolide) polymer (a PLGA).

The implants were made at a temperature high enough to melt thebimatoprost and soften the polymer, yet low enough to avoid loss ofsubstantial bimatoprost potency. The solubility parameters of thebimatoprost and the PLGA polymer used were similar so that thebimatoprost was soluble in the polymer thereby resulting in a solidsolution at the temperature used. An extruded implant made from a solidsolution of a therapeutic agent and a polymeric carrier can provide amore uniform and reproducible release profile of the therapeutic agent,as compared to an extruded implant where the bimatoprost is present as asolid dispersion in the polymeric carrier.

The polymer implants were made by melt extrusion in a piston drivenextruder or Daca extruder/microcompounder. The implants are rod-shaped,but can be made in any geometric shape simply by changing the extrusiondie.

The polymers were used as received from Boehringer Ingelheim and thebimatoprost was used as received from Torcan Chemical (Aurora, Ontario,Canada). To make an implant the polymer and bimatoprost were combined(see Table 2) in a Retsch ball-mill capsule with a ¼″ stainless steelball, and then the capsule was placed in the Retsch mill (Type MM200)for 5 min at 20-cycles/min. The capsule was then removed from the milland the powder blend was stirred with a spatula. The capsule with thepowder blend was mixed for 5 minutes on a Turbula mixer. The powderblend was inspected for homogeneity and the mixing procedure is repeatedif necessary.

A steel powder funnel and a spatula were used to transfer the powderblend to an extruder barrel mounted in a pneumatic compaction press. Asmall amount of powder blend was added to the extruder barrel and thepowder was compacted with the press set at 50 psi.

The powder-blend loaded barrel was placed in the extruder and allowed toequilibrate to a temperature of 65-71° C. The filaments were extruded at0.0025″/sec through a 720-micron circular die to form the rod-shapedimplant. The extruded filaments were smooth and had a consistentdiameter. The Implant formulations made are shown in Table 2.

The filaments were cut into one-milligram rods (approximately 2 mm long)and their drug release over time monitored in phosphate buffered salinepH 7.4.

TABLE 2 Bimatoprost Melt Extrusion Implant Formulations ImplantFormulations Bimatoprost wt % Polymer 1 Polymer 1 wt % 30 RG502 70 50RG502 50 30 RG752 30 50 RG752 50 30 RG504 30 50 RG504 50 30 RG755 30 50RG755 50

A bimatoprost containing polymer implant can be used to deliver acontrolled dose of bimatoprost to an ocular region to treat an ocularcondition over an extended period of time.

A bimatoprost implant can also be made using a low-melting polymer suchas a polycaprolactone. Additionally, instead of an extrusion method,direct compression of the polymer(s) with bimatoprost can be use to makea tablet implant suitable for intraocular use.

Example 6

Ultra Low Temperature Processes for Making Bimatoprost Implants

In this experiment we made additional bimatoprost containing polymericsustained release implants suitable for intraocular administration. Theimplants were made by a melt extrusion process we developed for conductat temperatures as low as about 57° C.

Exemplary implants made contained 15% bimatoprost (the therapeuticagent), 10% polyethylene glycol (PEG 3350) (the co-solvent or secondpolymer), and 75% poly (D,L,-lactide-co-glycolide) polymer (Resomer®RG752S, a PLGA) (the polymeric carrier or first polymer).

Typical extrusion temperatures for a PLGA implant are from about 85° C.to about 110° C. We determined that at an extrusion temperature of about80° C. or higher, 50% or less of the bimatoprost is therapeuticallyinactive (loss of potency). See FIG. 1. As shown by FIG. 1, fivedifferent formulation bimatoprost containing sustained release implantsor drug delivery systems (“DDS”) were made. Proceeding from left toright to left along the x axis of FIG. 1 these five formulations were:

TABLE 3 Bimatoprost DDS (Implant) Formulations shown in FIG. 1Formulation name 8092- 8092- 8092- 8092- 8092- 096G 102G 097G 103G 108GBimatoprost wt % 15 15 15 15 15 Polymer type RG504 RG504 RG504 RG752SRG752S wt % 75 70 65 70 75 PEG 3350 wt % 10 15 20 15 10

RG504 is a poly(D,L-lactide-co-glycolide (i.e. a PLGA) polymer resomerwhich is a 48:52 to 52:48 molar ratio (i.e. about 50:50) ofD,L-lactide:glycolide. RG504 has an inherent viscosity of 0.45 to 0.60dl/g in 0.1% chloroform at 25° C. (i.e. an average molecular weight ofabout 60,000) and is available from Boerhinger Ingelheim (Ridgefield,Conn.).

RG752S is also a poly(D,L-lactide-co-glycolide (i.e. a PLGA) polymerresomer, but comprises a 73:27 to 77:23 molar ratio (i.e. about 75:25)of D,L-lactide:glycolide. RG752S has an inherent viscosity of 0.16 to0.24 dl/g, at a 0.1 wt % concentration in chloroform at 25° C. and isalso available from Boerhinger Ingelheim (Ridgefield, Conn.).

The theoretical maximum potency of bimatoprost is by definition equal tothe label strength (“LS”) of the bimatoprost. For example, the labelstrength of a one milligram implant which comprises 150 μg ofbimatoprost is 150 μg. Thus, if that implant is assayed and determinedto release all 150 μg of the bimatoprost it contains over a certain timeperiod, it can be said that the implant had a100% potency. We determinedthe potency of the bimatoprost released from the implants made as apercent of their label strength using HPLC (high pressure liquidchromatography). Thus, the bimatoprost implants (each weighing about 1mg) made were dissolved in 0.5 mL acetonitrile in a 10 mL volumetricflask and sonicated for 5 min. The flask was then filled to volume withdiluent (72:18:10 water:acetonitrile:methanol); mixed well, andtransferred to a HPLC vial for analysis.

The HPLC analysis was performed using a Waters Alliance 2695 HPLCsystem, Waters Symmetry®C18 reverse-phase column 4.6 mmX75 mm, and aWaters 2487 UV detector. The conditions for analysis were flow rate of1.5 m L/minute, UV wavelength of 210 nm, column temperature of 30° C.and mobile phase of 72:18:10 (water:acetonitrile:methanol, v/v/v) with0.03% (w/v) trifluoroacetic acid. The injection volume of samples andstandards assayed was 75 uL with a cycle time of 45 min.

As shown by FIG. 1, the potency of the bimatoprost released from the DDSmade increased from about 40% when the DDS was made by a melt extrusionprocess carried out at 85° C., to more than about 90% potency when theDDS was made by a melt extrusion process carried out at 57° C. Thus, thepotency of the bimatoprost was inversely proportional to the temperatureat which the melt extrusion process used to make the DDS was carriedout. The use of different resomers and presence of PEG 3350 in the DDSformulations has no relevance to this finding of higher temperaturebeing correlated to lower bimatoprost potency. In other words, the useof a different resomer, the use of a different resomer in a differentamount and the inclusion of a PEG 3350 in the DDS formulation did notaffect the temperature to which the bimatoprost was exposed.

Thus, knowing that bimatoprost is a heat sensitive therapeutic agent wedeveloped a very low temperature melt extrusion process for makingbimatoprost containing implants. To make a DDS by a melt extrusionprocess wherein at least about 50% of the bimatoprost is biologicallyactive (i.e. has a potency at least 50% of the LS) requires reducing theextrusion temperature to less than about 80° C. Since the melting pointof most resomers, including PLGAs, used to make a DDS exceeds about 80°C. it is not sufficient merely to lower the extrusion temperature, as todo so would merely provide a partially or poorly melted polymer in whichthe active agent is far from homogenously distributed. A non-homogenousdistribution of the active agent in the polymer of the DDS can result ina burst release effect followed thereafter by wide oscillations in theamount and rate of release of the active agent from the polymer. Such adeficient DDS would have no therapeutic utility.

The goal therefore was to make an extruded PLGA-bimatoprost implant by aprocess that reduces the extrusion temperature and yet maintains ahomogenous mixture of (preferably non-crystalline) bimatoprost withinthe polymeric matrix of the DDS (implant).

We determined based on an analysis of solubility parameters, thatbimatoprost is soluble in the PLGA polymers (the polymer carriers orfirst polymers) used. Hence a solid solution of the bimatoprost and thepolymers used can be formed as the polymers are heated. Forming a solidsolution of a bimatoprost and a PLGA at a low temperature can avoid theoccurrence of substantial loss of bimatoprost potency. Additionally,forming a solid solution of the bimatoprost and a similar solubilityparameter PLGA (through use of a suitable co-solvent) has the additionaladvantage that the bimatoprost is prevented from re-crystallizing in thefinal extruded implant, since the implant is a solid solution of thebimatoprost and the PLGA in the co-solvent. Hence, no bimatoprostpolymorphs are present in the implant. Finally, the bimatoprost ishomogenously distributed throughout the polymer, as compared to thedistribution of the bimatoprost in the solid dispersion that is madewhen the bimatoprost and a PLGA are mixed together, the polymer meltedand the melted mixture extruded to make a DDS. In a solid dispersionimplant the bimatoprost is present in the form of crystals or particlesof the bimatoprost.

As noted, the PLGA polymers are not sufficiently molten at the lowerextrusion temperatures needed to retain the potency of bimatoprost aboveabout 50% of LS. We discovered that by addition of a low-meltingpolymeric cosolvent (such as a PEG) with the same (or substantially thesame) solubility parameter as the bimatoprost and the polymer usedpermitted the extrusion temperature to be lowered to as low as 57° C.The potency of the bimatoprost was thereby preserved. Additionally, wefound that the PEG containing DDS formulations we developed has areduced “burst” release normally associated with drugs as water solubleas bimatoprost. FIGS. 2 and 3 show respectively the total percentbimatoprost release and the daily microgram of bimatoprost released froman exemplary DDS formulation we made: in both FIGS. 2 and 3 theformulation observed was the Table 3 8092-108G formulation.

FIG. 2 shows the total amount of bimatoprost released from the 8092-108GDDS over a fifty day period. From about day 8 to about day 40 (a 32 dayperiod) the release rate was linear. FIG. 3 shows the daily amount ofbimatoprost released from the 8092-108G DDS over a fifty day period.From about day 13 to about day 42 (a 29 day period) the daily releaserate was between about 3.3 μg of bimatoprost per day and 2.5 μg ofbimatoprost per day, meaning that during that 29 period the daily rateof release did not vary by more than about 32%. From about day 13 toabout day 38 (a 25 day period) the daily release rate was between about3.3 μg of bimatoprost per day and 3.0 μg of bimatoprost per day, meaningthat during that 25 day period the daily rate of release did not vary bymore than about 10%.

Our selection of a PEG as a cosolvent for the bimatoprost and the PLGAwas based upon our analysis and comparison the solubility parameters ofthe three components (PEG, bimatoprost and PLGAS) of the DDS. Thus thesolubility parameters set forth in Table 4 show that bimatoprost can bepredicted to be soluble in both PLGA polymer and in PEG 3350.Furthermore, comparison the respective solubility parameters shows thatthe PEG 3350 can be predicted to be soluble in the PLGA. Hence it can bepredicted that upon melting the PEG 3350 at it's low melt temperature,the PEG 3350 can effectively plasticizing the PLGA and allow it to beextruded at the lower PEG 3350 melt temperature. This same principle canbe applied generally to other low-melting polymers such aspolycaprolactones as long as their solubility parameter does not differfrom the drug and PLGA by more than 10 (MPa)^(1/2). Other polymers canbe used to provide different blending and release characteristics. Ourpreferred formulation method is melt extrusion, but a suitable implantcan also be made by direct compression or solvent casting of thepolymer(s) with bimatoprost. The implants we made in this experimentwere cylindrically shaped but suitable implant can also be made withother cross-sectional shapes by changing the extrusion die.

The polymer implants we made in this experiment were made by meltextrusion at temperatures as low as 57° C. using a Dacaextruder/microcompounder (Daca Instruments, Inc., Goleta, Calif.). ThePLGA resomers (polymers) were used as received from BoehringerIngelheim. PEG 3350 and the bimatoprost were used as received from SigmaAldrich, and Torcan Chemical, respectively. The polymers (PLGA and PEG3350) and bimatoprost were combined in a stainless steel container withtwo ¼″ stainless steel balls and mixed on a Turbula mixer for 15minutes. The container was removed and the content is stirred with aspatula. It was then returned to Turbula mixer for an additional 15minutes, after which the powder blend was inspected for homogeneity andthe mixing procedure repeated if necessary.

The powder-blend was fed into the extruder at a controlled rate. Thefilament DDS was extruded through a 720 micron diameter circular dieforming cylindrically-shaped implant. The extruded filaments had asmooth surface with a consistent diameter. The filaments are cut intoone-milligram rods (approximately 2 mm long) and then placed intophosphate buffered saline pH 7.4 (0.01M) where their drug release inmonitored in vivo over time by HPLC.

TABLE 4 Solubility Parameters for DDS Components Component SolubilityParameter, MPa^(1/2) Bimatoprost (192024) 17-19 Resomer ® RG752s 21Polyethylene Glycol 3350  20^(c)

In Table 4 MPa is an abbreviation for milli-Pascals.

All references, articles, publications and patents and patentapplications cited herein are incorporated by reference in theirentireties. While this invention has been described with respect tovarious specific examples and embodiments, our invention is not limitedthereto and that it can be variously practiced within the scope of thefollowing claims.

We claim:
 1. A low temperature process for making an intraocularimplant, the process comprising the steps of: (a) combining a cycliclipid therapeutic agent and a polymer to form a mixture; (b) heating themixture to a temperature between about 50° C. and about 80° C., and; (c)extruding the heated mixture, thereby making an implant suitable forintraocular use.
 2. The process of claim 1, wherein the cyclic lipidtherapeutic agent is selected from the group consisting ofprostaglandins, prostaglandin analogs, and mixtures thereof.
 3. Theprocess of claim 1 wherein the cyclic lipid therapeutic agent isselected from the group consisting of bimatoprost, bimatoprost analogs,latanoprost, latanoprost analogs, travoprost, travoprost analogs,unoprostone, unoprostone analogs, prostaglandin E1 and prostaglandin E1analogs, prostaglandin E2 and prostaglandin E2 analogs, and mixturesthereof.
 4. The process of claim 3 wherein the cyclic lipid therapeuticagent is selected from the group consisting of bimatoprost, bimatoprostanalogs, and mixtures thereof.
 5. The process of claim 1 wherein thepolymer is a biodegradable polymer.
 6. The process of claim 5 whereinthe biodegradable polymer is selected from the group consisting ofpolylactic acid, polyglycolic acid, polylactide-co-glycolide, andcopolymers thereof.
 7. The process of claim 1 wherein the polymercomprises from about 30% to about 95% by weight of the implant.
 8. Theprocess of claim 1 wherein the cyclic lipid therapeutic agent comprisesfrom about 5% to about 70% by weight of the implant.
 9. The process ofclaim 1, wherein a potency of the cyclic lipid therapeutic agentreleased from the implant is at least about 50% of its maximum potency.10. A low temperature process for making an intraocular implant, theprocess comprising the steps of: (a) combining a prostaglandin analogand a biodegradable polymer to form a mixture; (b) heating the mixtureto a temperature between about 50° C. and about 80° C., and; (c)extruding the heated mixture, thereby making an implant suitable forintraocular use.
 11. The implant made by the process of claim
 1. 12. Aprocess for making an intraocular implant, the process comprising thesteps of: (a) combining: (i) a cyclic lipid therapeutic agent; (ii) afirst biodegradable polymer, and; (ii) a second biodegradable polymer toform a mixture, wherein; (α) the first biodegradable polymer and thesecond biodegradable polymer are different polymers; (β) thesolubilities of the cyclic lipid therapeutic agent, the firstbiodegradable polymer, and the second biodegradable polymer aresubstantially similar, and; (γ) the melt temperature of the secondbiodegradable polymer is lower than the melt transition temperature ofthe first biodegradable polymer, (b) heating the mixture to the lowermelt temperature of the second biodegradable polymer, so that the secondbiodegradable polymer can function as a solvent for the cyclic lipidtherapeutic agent and for the first biodegradable polymer, wherein themelt temperature of the second biodegradable polymer is lower than thetemperature at which the cyclic lipid therapeutic agent exhibits asubstantial loss of potency, and; (c) extruding the heated mixture,thereby making an implant suitable for intraocular use.
 13. The processof claim 12, wherein the cyclic lipid therapeutic agent component isselected from the group consisting of prostaglandins, prostaglandinanalogs, and mixtures thereof.
 14. The process of claim 12 wherein thecyclic lipid therapeutic agent is selected from the group consisting ofbimatoprost, bimatoprost analogs, and mixtures thereof.
 15. The processof claim 12 wherein the first biodegradable polymer is selected from thegroup consisting of polylactic acid, polyglycolic acid,polylactide-co-glycolide, and copolymers thereof.
 16. The process ofclaim 12 wherein the second biodegradable polymer is selected from thegroup consisting of decafluorobutane, poly(isobutylene),poly(hexemethylene adipamide), poly propylene, poly ethylene andpolyethylne glycol.
 17. The process of claim 12 wherein the solubilitiesof the cyclic lipid therapeutic agent, the first biodegradable polymer,and the second biodegradable polymer are all within about 10 Mpa^(1/2)of each other.
 18. The process of claim 12 wherein the solubilities ofthe cyclic lipid therapeutic agent, the first biodegradable polymer, andthe second biodegradable polymer are all within about 15 to 30Mpa^(1/2).
 19. The process of claim 12 wherein the first polymercomprises from about 30% to about 90% by weight of the implant.
 20. Theprocess of claim 12 wherein the second polymer comprises from about 50%to about 30% by weight of the implant.
 21. The process of claim 12wherein the cyclic lipid therapeutic agent comprises from about 5% toabout 30% by weight of the implant.
 22. A process for making anintraocular implant, the process comprising the steps of: (a) combining:(i) a prostaglandin analog, wherein the prostaglandin analog comprisesfrom about 5% to about 30% by weight of the implant; (ii) apoly(lactide-co-glycolide) copolymer, wherein thepoly(lactide-co-glycolide) comprises from about 30% to about 90% byweight of the implant. and; (ii) a second biodegradable polymer to forma mixture, wherein the second biodegradable polymer comprises from about5% to about 40% by weight of the implant, and wherein; (α) the apoly(lactide-co-glycolide) copolymer and the second biodegradablepolymer are different polymers; (β) the solubilities of theprostaglandin analog, the poly(lactide-co-glycolide) copolymer, and thesecond biodegradable polymer are all within about 10 Mpa¹¹² of eachother, and; (γ) the melt temperature of the second biodegradable polymeris lower than the melting point of the a poly(lactide-co-glycolide)copolymer, (b) heating the mixture to the lower melt temperature of thesecond biodegradable polymer, so that the second biodegradable polymercan function as a solvent for the prostaglandin analog and for the apoly(lactide-co-glycolide) copolymer, and; (c) extruding the heatedmixture, thereby making an implant suitable for intraocular use, whereinthe prostaglandin analog released from the implant has a potency of atleast about 50%.
 23. A method for treating an ocular condition, themethod comprising the step of intraocular administration of the implantmade by the process of claim
 1. 24. The method of claim 23, wherein theintraocular administration is selected from a location selected from thegroup consisting of the anterior chamber, the posterior chamber, thevitreous cavity, the choroid, the suprachoroidal space, the subretinalspace, the conjunctiva, the subconjunctival space, the episcleral space,the intracorneal space, the epicorneal space, the sclera, the parsplana, surgically-induced avascular regions, the macula, the retina andsub-tenon locations.